Patient support, wheelchair comprising a patient support and method for the automated calibration of a patient support

Abstract

The invention relates to a patient support (101), preferably a seat cushion, comprising a support region (1) having a base (2), a plurality of fluid cells (3) arranged on a seat side of the base (2), a pump (4), and a control unit (5), wherein one or more fluid cells (3) each define a pressure zone (6) and each pressure zone (6) is connected to the pump (4) by at least one zone valve (7), wherein each zone valve (7) is able to be actuated by the control unit (5) such that the control unit (5) is able to set a pressure in each pressure zone (6), characterized in that the patient support (101) comprises at least one pressure sensor (8) for measuring the pressure in at least one pressure zone (6), preferably at least one pressure sensor (8) per pressure zone (6).

Description

[0001] A patient support, a wheelchair comprising a patient support and a method for automated calibration of a patient support

[0002] The invention relates to a patient support, a wheelchair comprising a patient support and a method for the automated calibration of a patient support.

[0003] Pressure ulcers are tissue damage caused by sustained pressure and shear stress. Such stress typically occurs in immobile patients, such as those confined to bed or wheelchairs.

[0004] Patient supports consisting of a multitude of fluid cushions are known in the art. These can be subjected to a specific pressure, so that the patient resting on the fluid cushion is not exposed to a permanently constant pressure load despite being immobile.

[0005] EP 2 8924 89 A1 discloses a uniformly inflatable mattress with a pressure sensor to support patients and prevent bedsores.

[0006] EP 1 643 882 A1 discloses a cell cushion and method for producing a cell cushion which increases the surface area for supporting seated persons so that blood circulation through the tissue can be ensured.

[0007] EP 2 731 567 A2 concerns a patient

[0008] / Disabled transport device that distributes pressure on a patient using a variety of inflatable cushions. However, the existing patient supports are not flexible and cannot be easily adjusted to the patient's individual tissue, allowing specific areas to be particularly relieved.

[0009] The state of the art lacks a patient support that allows simple and intuitive operation and can be used flexibly in order to avoid damage to a patient's tissue, in particular due to insufficient blood flow to the tissue.

[0010] Furthermore, the current state of the art lacks a patient support that prevents the patient from being positioned in a one-sided position. Furthermore, the current state of the art lacks an adjustable patient support that adapts to the patient's orientation and positioning on the support and / or to the patient's individual needs.

[0011] The object of the present invention is to overcome these and other disadvantages of the prior art. In particular, the invention is intended to provide a simple patient support for relieving pressure on the vulnerable areas of a patient. Furthermore, an automated patient support, in particular a patient support that allows separate relief of pressure on particularly vulnerable areas of a patient without compromising seating stability, is to be provided.

[0012] This object is achieved by a patient support, a wheelchair, and a method as defined in the independent claims. Further embodiments are disclosed in the dependent claims.

[0013] The patient support according to the invention comprises a support area with a base, a plurality of fluid cells, a pump and a control unit. The patient support is preferably a seat support, e.g. a cushion. The plurality of fluid cells are arranged on a seat side of the patient support. One or more fluid cells each define a pressure zone. Each pressure zone is connected to the pump by at least one zone valve. Each zone valve can be actuated independently of the control unit, so that a pressure in each pressure zone can be set by the control unit. The patient support comprises at least one pressure sensor for measuring the pressure in at least one pressure zone. At least one pressure sensor is preferably arranged per pressure zone.

[0014] The terminology "protect / relieve" in this context means that areas are exposed to a lower overall pressure and / or lower localized pressure in one area of ​​the patient. This can be achieved, for example, by distributing the weight force over a larger area and / or by subjecting other areas to greater pressure to compensate for the weight force acting on the area to be protected / relieved.

[0015] The terminology "support" in this context means that areas of the patient are supported evenly and over as large an area as possible, so that stable positioning is possible.

[0016] The patient support can also include an energy storage device, e.g., a rechargeable battery, for power supply. This has the advantage that the patient support can be used mobile and is not dependent on a local power supply. Alternatively, the pressure sensor can be located in the pump, in a fluid cell, a supply to the pressure zones, or a supply to the pump's fluid cells.

[0017] The pressure sensor can be fluidly connected or fluidly connectable to multiple pressure zones, preferably via a common supply to the pressure zones. The pressure zones can preferably be selectively connected to the pressure sensor, for example via the valves, in particular zone valves.

[0018] Thus, exactly one pressure sensor, in particular exactly one pressure sensor, can be installed to measure multiple pressure zones depending on the opening states of the valves, in particular zone valves. The pressure of different pressure zones can be measured independently of one another, for example, if only one zone valve is open.

[0019] The pressure sensor can be arranged in the supply or pressure zone, preferably in the fluid cell, in particular adjacent to the inlet and / or outlet valve, thus simplifying the electrical design. In particular, the pressure sensor can be arranged in the direction of gas flow during application, downstream of the zone valve, downstream of the inlet valve, or upstream of the outlet valve.

[0020] One or more pressure zones can comprise at least two fluid cells that are fluidically connected to each other. This allows for a simpler patient support structure, as fewer valves and / or supply lines are required.

[0021] Alternatively, each pressure zone can be formed by exactly one fluid cell. The at least two fluid cells of the pressure zone can be arranged directly adjacent to one another. Preferably, a pressure zone with at least two fluid cells has a common supply to jointly supply them with pressurized fluid. This can simplify the design of the patient support.

[0022] In addition, at least two fluid-connected fluid cells of the pressure zone can be spaced apart from one another by at least one other fluid cell of a different pressure zone. This allows for a simpler design of the patient support, since several spaced-apart fluid cells can be subjected to the same pressure of a pressure zone without the need for separate components, particularly valves.

[0023] The fluid cell can be formed integrally with the seat side of the base, in particular the entire base. Such a fluid cell is thus spatially fixed relative to the base.

[0024] Alternatively, the fluid cell may be completely enclosed by an inner wall of the fluid cell and have at least one opening for a fluid supply and / or connection to another fluid cell. Such a fluid cell may be connected to the base only through the supply. However, the fluid cells are preferably fixed in one form relative to the base.

[0025] The patient support can comprise a sinkage sensor. The sinkage sensor is adapted to detect a sinkage depth. For example, the sinkage sensor can be adapted to detect whether a predefined sinkage depth is exceeded. The sinkage depth can be detected as a curvature or an angle of an inner wall section. Alternatively, the sinkage depth can be detected by a reduction in the distance between two inner wall sections or a partial section between the two inner wall sections, in particular relative to the maximum distance between the two inner wall sections or the partial section.

[0026] The inner wall section borders on the support areas so that the sinking depth in an operating position of the patient support can be detected essentially in a vertical direction.

[0027] The intrusion sensor may comprise a contactless measuring device, in particular an optical or acoustic device. In particular, the intrusion sensor may comprise an interferometer, a light barrier, or a time-of-flight measuring device.

[0028] The sinking sensor can be arranged partially or completely in a pressure zone, in particular in a fluid cell.

[0029] The indentation sensor may be configured to detect contact between an inner wall portion of at least one fluid cell and another element. The other element may preferably be an opposing inner wall portion of the fluid cell, the base, and / or the indentation sensor.

[0030] The sinking sensor can be located in a single fluid cell or in multiple fluid cells, for example, in a central area of ​​the patient support. This saves material costs and allows calibration of the patient support based on the areas of the patient that sink the most.

[0031] Additionally or alternatively, the sinking sensor can be arranged in a rear half of the patient support, preferably in a rear third of the patient support, and / or in a side area, so that, for example, a detection of the sinking of the ischial tuberosities and / or the coccyx area can be detected.

[0032] For example, contact can be detected by closing an electrical circuit through at least two electrodes of the intrusion sensor. One of the two electrodes can be arranged on one of the inner wall portion of the fluid cell, the base, or the intrusion sensor. The other of the two electrodes can be arranged on the same or a different one of the inner wall portion, the base, or the intrusion sensor.

[0033] Such a sinking sensor can be particularly reliable and robust against defects because it has a simple design and few parts that move relative to each other. Furthermore, the sinking sensor is thus independent of environmental influences that could affect a capacitive sensor, for example.

[0034] The indentation sensor can also be designed to determine a spatial position of the contact, for example by having a network of contacts.

[0035] The intrusion sensor can alternatively or additionally comprise a resistive, inductive, or capacitive sensor for detecting contact. The intrusion sensor can comprise two sections that are at least partially movable relative to one another. Alternatively or additionally, the intrusion sensor can be designed to be at least partially deformable in one direction. The intrusion sensor is preferably configured to trigger before the maximum intrusion depth is reached.

[0036] This makes it possible for the sinking sensor to detect before the patient's endangered area is no longer adequately protected / relieved.

[0037] The two sections of the sinking sensor can be movable perpendicular to each other.

[0038] Such a sinking sensor can trigger when a predefined deformation of the sinking sensor occurs.

[0039] The sensor can be elastically deformable, allowing it to return to its original shape when the deforming force is removed. An elastically deformable sensor also allows for a certain cushioning effect for the patient, even in the event of a defect.

[0040] The patient support may be a seat support and designed for use on a wheelchair. The seat support may have a maximum extension in the direction parallel to the support area of ​​65 cm, preferably 55 cm.

[0041] When patients are seated in a wheelchair, the ischial region, particularly the ischial tuberosity and the coccyx region, is subject to particular strain. A seat cushion designed specifically for a wheelchair allows for optimized transitions between patient positions and can prevent damage to the overlying tissue, for example, in the area of ​​the ischial tuberosity.

[0042] The patient support may have a thickness perpendicular to the support area in a range from 4 cm to 20 cm, in particular a thickness in a range from 4 cm to 15 cm or from 4 cm to 10 cm.

[0043] Such dimensions of the patient support allow for easy transport. Furthermore, pressure distribution on the patient can be optimized by maximizing the contact area of ​​the patient support, thus protecting the vulnerable area by ensuring the patient support is wide enough to adapt to the patient's contours.

[0044] The at least one printing zone may have a different shape or area in plan view than another printing zone.

[0045] In addition, a fluid cell of one pressure zone can have a different shape or area in plan view of the patient support than another fluid cell, in particular of the same pressure zone.

[0046] The different shape or surface of the pressure zones / fluid cells makes it possible to better adapt the pressure zone / fluid cell to particularly vulnerable areas and to the contours of a patient.

[0047] One or more pressure zones / fluid cells can form a supporting structure around a pressure zone for accommodating the most vulnerable parts of a patient in order to relieve them. The patient support can have an outlet valve and an inlet valve. The inlet valve can be fluidically connected to a pump. The outlet valve and inlet valve can be fluidically connected to at least one zone valve, preferably at least two zone valves, and particularly preferably all zone valves.

[0048] The patient support preferably has exactly one outlet valve and / or preferably exactly one inlet valve. This has the advantage that the number of valves required for the patient support can be reduced. Only one additional zone valve per zone is sufficient, eliminating the need for separate outlet and inlet valves for the individual pressure zones.

[0049] In addition, the patient support can have a three-way valve so that the function of the outlet valve and inlet valve can be fulfilled by the three-way valve.

[0050] At least one valve, preferably all valves, of the group of the inlet valve, the outlet valve and the zone valve can be closed when de-energized and preferably comprise a check valve.

[0051] The backflow of fluid can be prevented in particular by a mechanical return element, in particular comprising a spring and a seal, of the check valve, so that no active energization of the valve in a closed state is required.

[0052] A normally closed valve reduces the risk of failure and also ensures that, in the event of a power loss, the fluid cannot completely escape from a pressure zone. The pump and / or an exhaust silencer can operate at a noise level of less than 30 dB, preferably less than 25 dB, and particularly preferably less than 20 dB, for example, measured at a maximum distance of 1 m from the patient support.

[0053] A low noise level of the pump and / or the exhaust silencer allows the patient support to operate without disturbing the patient or people nearby, especially in the work environment, in everyday life or while sleeping.

[0054] The pump can be a diaphragm or ultrasonic pump. A diaphragm pump is particularly resistant to continuous stress and contamination. This allows for a more durable patient support despite long-term operation.

[0055] The patient support may include an elastic cover. The cover is adaptable along a contour of the fluid cells when the weight of a patient is applied to the cover, without causing a significant force parallel to the support area.

[0056] In this context, a significant force can typically be understood as a force parallel to the support area, the magnitude of which is approximately less than 5 percent of the patient's weight acting on the cover. Additionally or alternatively, the cover can also be designed so that a tensile stress in the cover of less than 30%, in particular 20%, of the contact pressure caused by the patient's weight acting on it.

[0057] By applying a small force, parallel or perpendicular to the support area, the tensile stress of the cover can be minimized, so that a so-called hammock effect can be avoided.

[0058] The hammock effect refers to the support effect on the patient by the cover, which can distort the desired support effect by the fluid cells.

[0059] The cover may comprise a macroscopically stretchable structure. This macroscopically stretchable structure may have stitched or folded regions, protrusions, and / or depressions. This macroscopically stretchable structure enables reduced tensile stress on the cover when subjected to a force, particularly the weight of a patient.

[0060] Such a cover allows the patient to be supported as elastically as possible by the fluid cells while lying down, thus avoiding tension in the cover. Furthermore, the cover distances the patient from the often poorly breathable material of the fluid cells, thus allowing for better ventilation of the overlying tissue.

[0061] The cover can also be permeable to air. This allows moisture to be more easily removed from the support area and improves ventilation of the patient's resting areas.

[0062] The covering may comprise or consist of a plastic, in particular a foam, preferably an open-cell / open-pore foam.

[0063] The patient support may include at least one humidity sensor and / or temperature sensor for measuring the humidity and / or temperature on the seat side of the base. The control unit may be configured to adjust the air supply / exhaust from the spaces between the fluid cells based on the measured humidity and / or temperature, in particular by means of at least one additional ventilation valve.

[0064] Alternatively or additionally, the patient support can include a visual or audible notification element that can be activated by the control unit. The notification element can indicate an exceeded measured value or a defect by means of a light source or a loudspeaker sound. For example, if a zone valve is defective, or if the temperature, humidity, and / or pressure of a fluid cell / pressure zone is exceeded or undershot, an alarm sound can indicate the defect.

[0065] Such humidity and / or temperature sensors can detect increased skin moisture / development of skin moisture at an early stage, which represents an additional risk factor for the development of tissue damage in the patient.

[0066] The patient support may include a ventilation device for supplying and / or removing fluid on the seat side of the base. The ventilation device may be operable by the pump.

[0067] The ventilation device can be switched and / or adjusted, preferably by the control unit, on the basis of a user input, a humidity measurement of the humidity sensor and / or a temperature measurement of the temperature sensor.

[0068] The ventilation device can be a fan, a

[0069] A pump and a ventilation system with fluid supply and discharge lines can be included. Thus, fluid can be supplied to and from the seating area via the ventilation device.

[0070] The fluid supply / discharge can be connected, for example via a vent valve, to the space between the fluid cells, preferably to a plurality of spaces. Furthermore, the fluid supply / discharge can have a plurality of fluid supply channels that lead to different spaces between the fluid cells in the seat area.

[0071] The ventilation device may also comprise a dehumidification unit which is configured to reduce the moisture content of supplied fluid by a method known to the person skilled in the art, in particular based on a heat exchange.

[0072] In this context, it would also be conceivable that the ventilation device is configured to dehumidify an interior of the fluid cells, the valves and / or the supply, for example to compensate for condensation due to pressure differences.

[0073] The control unit or an additional computer system of the patient support can be configured to detect temporal pressure changes in at least one pressure zone using at least one pressure sensor and / or sinking sensor and to assign them to an activity pattern. For example, the control unit can measure pressure values ​​at regular intervals. Alternatively, a frequency of pressure changes can be measured, such as can occur during exercise.

[0074] The temporal pressure changes can be recorded, for example, by repeatedly measuring within predefined time intervals, or by detecting the time of the pressure change depending on whether predetermined pressure changes are exceeded.

[0075] In this context, the activity pattern is typically a temporal sequence of pressure changes in the pressure zones due to movements of the patient, which have a defined periodicity and / or intensity.

[0076] For example, a low-intensity pressure change that occurs rarely over a longer period of time, such as when the patient is sleeping, can be attributed to a particular activity pattern.

[0077] The activity patterns can include a high-activity pattern such as exercising, moderate-activity pattern such as eating or reading, and / or low-activity pattern such as resting or sleeping. The activity pattern can also be assigned to the patient's individual movement pattern.

[0078] The assignment of an activity pattern can be performed using a predefined algorithm, in particular by exceeding predefined thresholds. The thresholds can, for example, represent a predetermined frequency, periodicity, and / or intensity of pressure changes within a predefined period. The algorithm can also be adapted to the patient's weight.

[0079] Alternatively, the assignment of an activity pattern can be performed through classification using machine learning. The algorithm or machine classification for assigning an activity pattern can be patient-specific, particularly based on the patient's anatomy.

[0080] By assigning a specific activity pattern, the control unit can optimize control so that tissue damage can be prevented during any activity of the patient.

[0081] The patient support can be operated in a first and a second operating mode. It is also conceivable to provide additional operating modes. The control unit can be configured to control the pressurization of the pressure zones, so that the first operating mode has a first pressure ratio between at least two pressure zones. In the second operating mode, a second pressure ratio, different from the first, can be set between the two pressure zones.

[0082] The control unit may be configured to change the operation mode based on the detection of a particular activity pattern.

[0083] The different operating modes allow individualized adjustment of the pressure applied to the patient support to the needs of a patient.

[0084] The control unit can be designed in such a way that in the first or second operating mode, a temporally repeated pressure application and pressure relief of at least one pressure zone, in particular groups of pressure zones, takes place.

[0085] By varying the pressure over time, it is possible to prevent a patient from being exposed to one-sided stress over a long period of time and thus to minimize tissue damage.

[0086] The control unit can alternatively or additionally be designed in such a way that in the first or second operating mode an activity pattern of a patient is detected and the pressure applied to the pressure zones is adapted to this activity pattern.

[0087] The control unit can alternatively or additionally be designed in such a way that in the first or second operating mode the pressure zones are pressurized to ensure stable positioning of the patient.

[0088] The patient support is therefore suitable for a wide range of applications with different patient activity patterns.

[0089] The control unit can alternatively or additionally be designed such that in the first or second operating mode, the fluid cells, preferably all fluid cells, are pressurized up to a maximum pressure.

[0090] Pressurization to the maximum pressure can simplify transport of the patient from or to the patient support.

[0091] The seat side of the base may not have a fluid cell in one area. Preferably, one edge of the base or an area adjacent to the edge is designed without fluid cells. The control unit and / or the pump can be arranged in this area of ​​the base. Certain areas of the patient support often do not accommodate particularly vulnerable parts of the patient, so that these areas do not necessarily have to be supported by fluid cells. By arranging the control unit / pump in one of these areas, a more compact patient support can be provided.

[0092] The control unit and / or pump can be arranged partially or completely in a common plane with the plurality of fluid cells. Thus, the thickness of the patient support perpendicular to the base can be reduced.

[0093] The control unit and / or pump can in particular be arranged in an area of ​​the patient support which, in the operating position, is intended to accommodate a part of the patient which is not particularly at risk of tissue damage.

[0094] The parts of the patient that are not particularly at risk are typically those that are located away from the patient's center of gravity and / or have an even weight distribution. For a seated patient, a part that is not particularly at risk is the lower thigh.

[0095] The patient support may have a pressure port. The pressure port allows at least one additional device to be pressurized by the pump if the additional device is connected to the patient support via the pressure port.

[0096] The pressure port may be closed in the standard state and can only be opened by connecting the additional device. The additional device may be an extension of the patient support, which is connectable to the patient support and in particular comprises one or more fluid cells that form at least one pressure zone.

[0097] The patient support can therefore be easily extended and adapted for a wide range of other applications.

[0098] A system may comprise a patient support as described above and such an additional device. Thus, in addition to supporting the patient's buttocks with the patient support, the system may also support the patient's back with the additional device. The additional device could also be another patient support.

[0099] A pressure relief valve can be assigned to at least one fluid cell and / or pressure zone, preferably at least one fluid cell per pressure zone.

[0100] A pressure relief valve can avoid peak loads on the fluid cells or pressure zones and thus prevent damage to the patient support.

[0101] The fluid cells can comprise or consist of a plastic. Preferred plastics are silicone, vulcanized rubber, polyurethane, polychloroprene, poly(organo)siloxane, polyisoprene, polyethylene, polypropylene, polystyrene, and / or polyester. The fluid cells preferably comprise or consist of a film material, in particular a plastic film. The plastic film preferably comprises or consists of one of the aforementioned plastics. These plastics are gas-tight and sufficiently elastically deformable.

[0102] The base can also be made of or comprise the described plastic materials. A base made of such a plastic material allows for a flexible base for the patient support, allowing it to optimally adapt to a support area, particularly a seat surface, such as that of a wheelchair.

[0103] The patient support may comprise a wireless communication interface for sending status data of the patient support and / or receiving user input data, in particular for selecting the operating mode for operating the patient support.

[0104] Such a wireless communication interface enables uncomplicated monitoring of the status data of the patient positioning and more convenient operation through user input.

[0105] The wireless communication interface can communicate with a user's terminal device, e.g. a smartphone, tablet, or laptop, preferably in a frequency band between 2.402 GHz and 2.480 GHz.

[0106] The patient support can comprise a data memory and a computing unit. The computing unit can calculate at least one target pressure value for at least one pressure zone based on at least one measured value from the sinkage sensor and / or the pressure sensor. The measured values ​​and / or the target pressure value can be stored in the data memory. The control unit can adjust a pressure in at least one pressure zone based on the target pressure value. The pressure within the fluid cells or pressure zones can be adjustable for a specific patient. In particular, the pressure can be adjustable on the basis of the pressure values ​​previously measured by the sensors, in particular pressure values ​​based on a previous calibration. In this way, the patient support can provide individual support that is optimized for each patient.

[0107] A wheelchair may include a patient support as described above.

[0108] The invention further relates to a method for the automated calibration of a patient support. The method is preferably used for calibrating a patient support as described above. The method comprises a step of placing a patient on the patient support such that a weight force is exerted on the patient support.

[0109] The pressure of at least one pressure zone is varied. The pressure at which a sinking sensor detects sagging is determined. The sagging can be detected by a sinking sensor as described above. In particular, sagging can mean that an inner wall section of at least one fluid cell in the pressure zone touches another element, preferably an opposite inner wall section of the fluid cell, a base, and / or the sinking sensor.

[0110] The measured pressure is saved.

[0111] By varying the pressure of at least one pressure zone, the depth of penetration can be measured as a function of the pressure. By measuring the depth of penetration, calibration can be further optimized. This procedure can be repeated for another pressure zone, a plurality of pressure zones (in particular two to five), or all pressure zones.

[0112] Using such a process, a patient support can be automatically adjusted to the individual needs of a patient. Depending on the patient's anatomy, particularly weight, size, and weight distribution across the fluid cells / pressure zones, a different pressure is measured, at which the sinking sensor detects a pressure zone.

[0113] Based on these values, the operating modes can be adapted to the patient. For example, a minimal pressure in the fluid cells can ensure that the patient does not sit through the procedure.

[0114] A target pressure value can be determined in at least one pressure zone based on the pressure determined by a pressure sensor at which the sinking sensor detects. Determining a target pressure value for a pressure zone enables patient-specific adjustment of individual pressure zones.

[0115] The sinking sensor can be arranged in a pressure zone. Based on the pressure determined by the pressure sensor, at which the sinking sensor detects, the pressure of the pressure zone and at least one adjacent pressure zone can be adjusted.

[0116] This allows not only the pressure change of a fluid cell / pressure zone to be taken into account, but also the interaction of a pressure change of a fluid cell / pressure zone on nearby, particularly neighboring, pressure zones. Increasing or decreasing the pressure of at least one neighboring pressure zone makes it possible to specifically relieve or load a specific pressure zone.

[0117] The invention will be described below with reference to certain

[0118] Embodiments and figures described that show :

[0119] Figure 1 : an oblique side view of a first

[0120] Design of a patient support;

[0121] Figures 2A and 2B: a cross-section D of the patient support of Fig. 1 without force and under force;

[0122] Figure 2C : a cross-section C of the patient support of Fig . 1 under force application;

[0123] Figure 3: a cross-section of a second embodiment of a patient support with a ventilation device;

[0124] Figures 4A and 4B : a cross section of a schematic

[0125] Illustration of a patient support with a cover with and without a force applied parallel to the cover;

[0126] Figures 5A and 5B: a first and second embodiment of a fluid cell with a sinking sensor in cross section;

[0127] Figure 6: an oblique side view of a wheelchair with the embodiment of the patient support according to Fig. 1; Figure 7A: a schematic representation of the valve control of a patient support according to

[0128] Fig. 2A to Fig. 2C;

[0129] Figure 7B: a schematic representation of the valve

[0130] Control of a patient support according to

[0131] Fig. 3;

[0132] Figure 8: an oblique side view of a user terminal for communication with a patient support;

[0133] Figures 9A to 9C: a first embodiment of a valve;

[0134] Figures 10A to 10C: a second embodiment of a valve;

[0135] Figure 11 : an oblique side view of a third

[0136] Design of a patient support.

[0137] Figure 1 shows an oblique side view of a first embodiment of the patient support 101 in the form of a seat cushion. This embodiment of the patient support 101 is intended for use in a wheelchair and has a seating area 1 arranged on a base 2 of the patient support 101. The base 2 is made of a flexible material such as polypropylene, polyethylene, or rubber, so that the base 2 can adapt to the contours of a surface, e.g., a wheelchair. Furthermore, the patient support 101 can thus be transported more easily.

[0138] The patient support 101 has a control area T in which a control unit is arranged. The control area T is arranged on one edge of the patient support 101 so that a patient can be placed on it with their lower thighs, since this part of the body is not particularly at risk of pressure ulcers. The control area T only has a flexible cushion for padding the patient and no fluid cell 3. Alternatively, however, it is conceivable to equip the control area with one or more fluid cells or pressure zones. The patient is adequately supported by the flexible cushion, the electronic components, and a pump within the control area T.

[0139] In addition, the patient support 101 has a plurality of fluid cells 3 made of polyurethane film, which together with the control region T form the seating region 1 and are materially connected to the base 2. The fluid cells 3 in Fig. 1 each form a pressure zone 6. Fig. 1 further shows seven pressure zones 6 for the primary support P and four pressure zones 6 for the secondary support S. However, it would also be conceivable for the area of ​​primary and secondary support P, S to comprise pressure zones formed by a plurality of fluid cells 3 (see Fig. 11). The fluid cells 3 are shaped differently so that the patient can be better supported. The geometric shape and size of the fluid cells 3 is tailored to the support requirements of a patient. The primary support P particularly relieves the patient's ischial tuberosities and coccyx area, as this area is particularly prone to pressure sores.Some side surfaces 104 of the fluid cells 3 of the primary support P and secondary support S are, in plan view, partially shaped at an angle to a rectangular edge region of the base 2 in order to frame the endangered region. In this way, the support of the patient can be optimized. In the rear region of the patient support 101 there is a pressure connection 24 which is provided for connecting to and supplying with compressed air from further devices. For example, it is possible to support the patient's back by a device that can be supplied with compressed air, in particular a further patient support that can be connected to the patient support 101. The cross section D through the central fluid cells 3 of the patient support 101, shown schematically in Fig. 1, is shown in Fig. 2A and Fig. 2B. The cross section C in an edge region of the patient support 101, shown schematically in Fig. 1, is shown in Fig. 2C.

[0140] Figure 2A shows a cross-section of the patient support 101 of Fig. 1 without any applied force. An elastic cover 15 is arranged on the seating area 1 and can be adapted to a contour 32 of fluid cells 3 (see Figs. 4A and 4B). The patient support 101 also has an electronic control unit 5, which is arranged in the control area T. A flexible foam cushion 51 is arranged above the control unit 5 and covers the entire control area T. The control area T does not have a fluid cell 3. A pump 4 is arranged within the control unit 5, with which the fluid cells 3 can be pressurized with compressed air by the pump 4 sucking in ambient air and feeding it to the fluid cells 3 through inlets 27. The pump 4 is a piezoelectric ultrasonic pump , which is known to those skilled in the art , and causes a noise level of less than 20 dB at a distance of one meter during operation .In addition, the control unit 5 has a pressure gauge 8 for measuring the pressure of the pressure zones 6. In Fig. 2A to Fig. 2C, the pressure gauge 8 is connected to the control unit 5 and arranged at the end of the feed line 27 so that it can be fluidly connected to the pressure zones 6 in order to measure the pressure. Thus, in Fig. 2A to 2C, the pressure gauge 8 can be connected to different pressure zones 6 by valves which can be controlled by the control unit 5 in order to measure the pressure in the pressure zones 6 (not shown in Fig. 2A to 2C). The zone valves and inlet and outlet valves are all arranged in the area of ​​the control device 5 so that no additional lines for controlling the valves have to run through the base 2. In an alternative embodiment, however, each pressure zone has its own pressure gauge (see Fig. 7).

[0141] In addition, the two middle fluid cells 3 of the pressure zones 6 for primary support P each have a sinking sensor 9 which is connected to the control unit 5 and detects when a predefined sinking depth of the fluid cell 3 is exceeded (see Fig. 5A and 5B). The sinking sensor 9 in Fig. 2A and Fig. 2B is arranged in the lower region of the fluid cell 3 adjacent to the base 2 so that the exceeding of the sinking depth of the ischial or coccyx region of the patient, which sink particularly deeply, can be detected. This predefined sinking depth is achieved in Fig. 2B by an inner wall section 30 of the fluid cell contacting the sinking sensor 9 so that an electrical contact is closed (see Fig. 5A and Fig. 5B). The control unit 5 is configured to control the pump 4 on the basis of the measured pressure values ​​of the manometer 8 and / or the sinking depth of the sinking sensor 9.The individual pressure zones 6 can be supplied with compressed air separately by the pump 4 through separate feeds 27 with separate zone valves 7 (see Fig. 7).

[0142] For better visibility, only one supply 27 for compressed air to a pressure zone 6 in the primary supporting area P, which runs within a base 2, is shown in Fig. 2A to 2C. The three fluid cells 3 in Fig. 2B for the primary support P can, however, each be pressurized separately by a supply 27. The supplies 27 each have a zone valve in the area of ​​the control device 5, so that they can be selectively pressurized. The primary area P has been shown in dotted lines in Fig. 2A and Fig. 2B for better visibility. The fluid cells 3 are each connected to the base 2. Alternatively, the fluid cells 3, which form a common pressure zone 6, can be fluidly connected to one another by at least one line (see Fig. 11).

[0143] Figure 2A shows the patient support 101 without any force acting on it, so that no deformation of the seating area 1 occurs.

[0144] Figure 2B shows the patient support 101 with the acting weight force 16 of a patient 11 in the first operating mode 21. In this exemplary first operating mode 21 in Fig. 2B, the control unit 5 is configured to support the patient as evenly as possible by the fluid cells 3 and at the same time to prevent the patient 11 from sagging. The patient 11 should generally not be supported on a hard surface, except for calibration, but rather by the fluid cells. In particular, the patient should generally not sink down to the surface of the sinkage sensor 9. The control unit 5 in the first operating mode 21 is configured to ensure the greatest possible sinkage depth during proper operation, without triggering the sinkage sensor 9, so that a support surface that supports the patient 11 can be maximized.

[0145] For this purpose, the control unit 5 can be calibrated by reducing the pressure within at least one fluid cell 3. The sinking sensors 9 can thus detect at which fluid cell 3 and preferably at which pressure value of the manometer 8 the patient 11 exceeds the predefined sinking depth. Exceeding the predefined sinking depth, or the pressure value, is shown in Fig. 2B by contacting the upper inner wall section 30 of the fluid cell 3, which is deflected by the weight force 16, with the sinking sensor 9. By exceeding the predefined sinking depth, an electrical contact of a circuit of the sinking sensor 9 is closed and the sinking sensor 9 is triggered.

[0146] Alternatively, detection can occur by interrupting the electrical contact.

[0147] In addition, calibration with an initially unpressurized fluid cell 3 / pressure zone 6 would also be conceivable. For such a calibration, the pressure is increased instead of reduced in the fluid cell 3. The remaining fluid cells 3 can meanwhile be subjected to a reference pressure, in particular a minimum or maximum pressure. The sinking sensor 9 accordingly detects the pressure above which the inner wall section 30 no longer contacts the sinking sensor 9 due to the weight force 16, for example due to a loss or the establishment of electrical contact of the sinking sensor 9. The electrical circuit can therefore be closed or open when the inner wall section 30 makes contact with the sinking sensor 9 and conversely can be open or closed when the inner wall section 30 is moved away from the sinking sensor.

[0148] On the basis of this detected value or a plurality of such values ​​for different fluid cells 3, the control unit 5 can be calibrated for each patient. For this purpose, the control unit 5 has a computing unit with an internal electronic data memory. In particular, optimal target pressure values ​​for the fluid cells 3 can be determined by the computing unit of the patient support 101 and stored in the data memory. In this way, the operating modes 21, 22 can be adapted to the individual needs of the patient 11. The patient-specific values ​​and operating modes 21, 22 are stored for the patient in the data memory, so that no recalibration of the same patient 11 has to be carried out.

[0149] In addition, the preceding calibration can ensure that an upper inner wall section 30 of the fluid cell 3 cannot be deflected to the base 2 in the operating mode 21, 22. Depending on the operating mode 21, 22, the various pressure zones 6 can be pressurized with compressed air at a different pressure ratio to one another.

[0150] Figure 2C shows a cross-section of the patient support 101 with the acting weight force 16 of the patient in an edge region of the patient support 101 in a second operating mode 22. In this exemplary second operating mode 22, the control unit 5 is configured to particularly relieve a critical ischial or coccyx region 111 of the patient 11. For this purpose, the fluid cells 34 of a secondary support S around the fluid cell 33, which accommodates the critical coccyx region 111 of the patient 11, are pressurized to a greater extent with compressed air than the fluid cell 33, which accommodates the critical coccyx region 111. The region for the secondary support S has been shown in Fig. 20 with dense dots for better visibility, and the centric region for the primary support P has been shown with coarse dots.By varying the support of the adjacent regions 112 of the critical region 111, damage to the tissue of the patient 11, in particular the development of pressure ulcers, can be avoided. Fig. 2C shows only an example of a single fluid cell 33 forming a pressure zone 6 for accommodating the critical region 111. However, a pressure zone 6 comprising several fluid cells 3 is also conceivable, which is relieved by one or more adjacent pressure zones 6 (see Fig. 11).

[0151] The patient support 101 also has many different such operating modes 21, 22. The control unit 5 is also configured to automatically select and adapt the operating modes 21, 22 based on the movement of the patient 11.

[0152] The movement of the patient 11 is assigned to an activity pattern by measuring pressure changes over time in a pressure zone 6 by the manometer 8 and / or the sinking sensor 9. An operating mode 21, 22 is set or adjusted on the basis of the activity pattern. In addition, the control unit 5 is configured to switch between the operating modes 21, 22 more frequently depending on the assigned activity pattern, so that one-sided strain is avoided. In the case of an activity pattern with little movement of the patient 11, for example when the patient 11 is resting or sleeping, the operating mode 21, 22 is changed particularly frequently by the control unit 5. The change between operating modes 21, 22 is repeated periodically by the control unit 5.

[0153] In the case of an activity pattern involving a great deal of movement of the patient 11, such as during sports, a different operating mode 21, 22 is automatically set by the control unit 5. The operating mode 21, 22 is also configured by the control unit 5 such that the positioning of the patient is optimized during a great deal of movement by subjecting the supporting and less vulnerable area S of the patient support 101 to significantly greater compressed air pressure than a centric primary support area P.

[0154] The control unit 5 also has a wireless communication interface for sending and receiving data. The user can preferably easily connect a smartphone to the communication interface via an app. The user can thus view the status data of the patient support 101, in particular status data or patient data stored on a data memory of the patient support 101. In addition, the user can send an input to the communication interface in order to change the operating mode 21, 22, for example. The computing unit of the control unit 5 is also configured to make patient-specific adjustments to the operating modes 21, 22 based on the user input. Based on the user input, certain preferences for controlling the operating modes 21, 22, such as a time period after which the operating mode 21, 22 is changed, can be adjusted.In addition, the calibration of the patient support can be carried out by user input, saved and automatically assigned to the user.

[0155] In addition, the user can set an operating mode 21, 22 for transporting the patient 11. In this operating mode 21, 22, all fluid cells 3 are fully pressurized with compressed air, so that the patient 11 can be easily lifted and / or slid off the patient support 101.

[0156] Figure 3 shows a cross-section of a second embodiment of the patient support 101 with a ventilation device 20. The ventilation device 20 is connected to a pump 4 so that the ventilation device 20 can be operated with the pump 4. The ventilation device 20 has a plurality of accesses 201, 202 to the spaces 104 of the fluid cells 3. The accesses 201, 202 of the ventilation device 20 run through a base 2 of the patient support 101. The air circulation from a seat side of the base 2 of the patient support 101 is thus improved either by air supply or air removal, driven by the pump 4. A cover 15 over the fluid cells 3 is designed to be permeable to air so that the areas of a patient lying on them can be better ventilated. This has the advantage that the formation of moisture through perspiration from the contact areas can be reduced.The risk of the skin becoming soft due to moisture accumulation and the resulting reduction in skin resilience can thus be reduced.

[0157] Figure 3 also shows a control unit 5 which is connected to a humidity sensor 18 and a temperature sensor 19. The humidity and temperature sensors 18, 19 are partially arranged in the intermediate space 104 so that the temperature and humidity in a seating area 1 of the patient support 101 can be detected. Alternatively or additionally, one or more humidity and temperature sensors 18, 19 can be arranged between the fluid cells 3 of the particularly vulnerable area for primary support P. The area for primary support is shown in dotted lines in Fig. 3 for better visibility. In addition, the control unit 5 is connected to a manometer 8 and a sinkage sensor 9, as in Fig. 2A to Fig. 2C.

[0158] The control unit 5 has a computer unit that operates the ventilation device 20 based on the measured values ​​of the humidity and / or temperature of the humidity and temperature sensors 18, 19. The computer unit is also configured to control the patient support 101 based on a pressure determined by the manometer 8 and / or a detected depth of penetration of the penetration sensor 9, analogous to Figs. 2A to 2C.

[0159] Figures 4A and 4B show a cross-sectional view of a schematic representation of a first embodiment of the patient support 101 according to Fig. 2A and Fig. 2B with a macroscopically stretchable cover 15. Such a cover can also be used for the second embodiment in Fig. 3 or the third embodiment of the patient support 101 in Fig. 11.

[0160] No weight force acts on the cover 15 in Fig. 4A, so that a flexible structure, schematically represented by a jagged pattern, is not deformed. The cover 15 consists, for example, of an open-cell polyurethane foam, so that it can be deformed under low force while still allowing air to be supplied to the tissue of a patient lying on it.

[0161] The flexible structure can be deformed parallel to a hand with minimal force. The flexible structure is formed by seams, folds, and / or easily deformable material.

[0162] In Fig. 4B a weight force 16 acts on the coating 15.

[0163] The flexible structure 15 deforms in a direction 17 parallel to the cover 15 due to the applied weight force 16, but without generating strong tensile stresses in the cover 15. This prevents a "hammock effect," which could promote local damage to the patient's tissue due to tension in a cover. The patient's weight is thus absorbed essentially in a point-elastic manner by the fluid cells of the patient support located beneath the cover 15, with the cover 15 adapting to the contour of the fluid cells due to the weight force.

[0164] Figures 5A and 5B show two embodiments of a fluid cell 3 with a sinking sensor 9 in cross section. In Fig. 5A and Fig. 5B, a current source is connected to a first conductor 94 and / or second conductor 95. The sinking sensor 9 detects when these two conductors 94, 95 contact each other, thus closing an electrical circuit.

[0165] Alternatively, it could be detected when a circuit is interrupted or a detected resistance value of a circuit changes.

[0166] The embodiment of the fluid cell 3 in Figure 5A shows that, at a maximum sinking depth 91, an upper inner wall section 30 contacts the first conductor 94 of the fluid cell 3 with the second conductor 95. The second conductor 95 of the sinking sensor 9 is arranged on a side facing a base 2 at the bottom of the fluid cell 3, so that an acting weight force 16 triggers the sinking sensor 9.

[0167] The embodiment of the fluid cell 3 in Fig. 5B shows that the sinkage sensor 9 has two different sections 92, 93 which are movable relative to one another. Only the outer sections 92 of the sinkage sensor 9 are held by supports 96. The middle section 93, on the other hand, can be deflected downwards by the weight force 16 of a patient. The middle section 93 of the sinkage sensor 9 thus has a supporting effect, so that a patient is supported even if the fluid cell 3 is defective. In addition, the high degree of elasticity on contact prevents potentially damaging pressure from being applied to the ischial or coccyx areas to be protected. The maximum sinkage depth 91 of the fluid cell is significantly less than the overall width B of the fluid cell 3.

[0168] The first conductor 94 in Fig. 5B is electrically connected to the central section 93, and the second conductor 95 is electrically connected to a bottom of the fluid cell 3, which runs parallel to the base 2. Deflection of the central section 93 and contact with the bottom can thus trigger the sinking sensor 9 in Fig. 5B.

[0169] Figure 6 shows an oblique side view of a wheelchair 102 with an embodiment of the patient support 101 according to Fig. 1 with a plurality of fluid cells 3 on a base 2, which form a seating area 1. The patient support 101 can be used as a detachable seat cushion of the wheelchair 102 or can be rigidly connected to the wheelchair 102.

[0170] Figure 7A shows a schematic representation of the valve control of the embodiment of the patient support 101 according to Fig. 2A to Fig. 2C, with the difference that the patient support 101 has a separate manometer 8 for each pressure zone 6 for measuring the pressure in the pressure zone 6. The pressure zones 6 are each formed by a fluid cell 3. Alternatively, however, a pressure zone 6 can be formed by several fluid-connected fluid cells 3, so that the fluid cells 3 can each be pressurized with compressed air at a uniform pressure (see Fig. 11).

[0171] An ultrasonic pump 4 with an inlet valve 12 and an outlet valve 13 is arranged in a control area T of the patient support 101. The inlet valve 12 is connected to the diaphragm pump 4, so that a supply 71 to a plurality of zone valves 7 can be pressurized with compressed air. The outlet valve 13 is also connected to the supply 71 to the zone valves 7. Thus, one zone valve 7 is required per pressure zone 6 of an area for primary and secondary support P, S. The inlet valve 12 and outlet valve 13 can thus be used to supply compressed air to or release compressed air from all pressure zones 6. Thus, fewer valves 7, 12, 13 are required per pressure zone 6. The intake valve 12 and the exhaust valve 13 are also optimized for a low noise level of less than 20 dB at a distance of one meter. The exhaust valve 13 also features a noise damper 131 for this purpose.

[0172] For clarity, the plurality of zone valves 7 is represented by only two different pressure zones 6. However, the dotted area of ​​the supply line 71 indicates that the patient support 101 has additional pressure zones 6, each formed by a fluid cell 3. Alternatively, several fluid cells could also form a pressure zone. All valves 12, 13, 7 also have an electrical actuator 72, 132, 122, so that the valves 12, 13, 7 can be individually opened / closed electronically by a control unit.

[0173] In addition, the valves 12, 13, 7 include a non-return valve 14 as a safety measure, which is closed by a return spring 141 in a de-energized state. The non-return valve 14 can be opened by applying current to the control unit. Thus, compressed air can be supplied through the inlet valve 12 or discharged through the outlet valve 13.

[0174] Figure 7B shows a schematic representation of the valve control of the embodiment of the patient support 101 according to Fig. 3. The valve control in Fig. 7B is similar to Fig. 7A, but in contrast to Fig. 7A, also has a ventilation device 20. For a further description of the preceding features, reference is made to Fig. 7A.

[0175] The ventilation device 20 is provided with a fluid supply

[0176] 211, which are connected to the piezoelectric ultrasonic pump 4 via a ventilation valve 202, or alternatively a plurality of additional ventilation valves 202. The fluid supply 211 is divided, on a side facing the fluid cells, into a plurality of fluid supply channels 201, which run to a plurality of intermediate spaces 104 of the fluid cells 3. Thus, uniform ventilation of the intermediate spaces 104 of the patient support 101 can be achieved, so that skin moisture can be reduced and moisture accumulation can be avoided.

[0177] The venting valve 202 in Fig. 7B is shaped essentially analogously to the inlet valves 12, the outlet valve 13, and the zone valves 7 and also has a check valve 14 with a return spring 141 and an electrical actuator 203. The electrical actuator 203 can be controlled by a control unit to open the venting valve 202 so that fluid, in particular air, is fed through the fluid supply 211 from the piezoelectric ultrasonic pump 4 to the intermediate spaces 104. Thus, the ultrasonic pump 4 can be used both to supply the fluid cells 3 with fluid and for ventilation via the ventilation device 20.

[0178] Figure 8 shows a schematic representation of a user terminal in the form of a smartphone 27. The smartphone can be wirelessly connected to a communication interface of a patient support according to Fig. 2A to Fig. 3 via an app, so that it can send user inputs and read status data from the patient support. Furthermore, a user can set a preferred operating mode for the patient support through the user input (see Fig. 2A to 2C).

[0179] Figures 9A to 9C show a first embodiment of a valve 25 which can be used as an inlet, outlet, and / or zone valve 12, 13, 7 (see Fig. 7). The valve 25 has an open state 251 which allows compressed air to flow through the valve. The valve 25 also has a blocking state 252 in which no compressed air can flow through the valve 25. As a safety measure, the valve 25 is in the blocking state 252 when de-energized. The blocking state 252 of the valve can be transferred to the open state 251 by actuating an electronic actuator 132 against a restoring force of a return spring 141.

[0180] Figures 10A to 10C show a second embodiment of a valve 26, which can be used as an inlet, outlet, and / or zone valve 12, 13, 7 (see Fig. 7). The valve 26 is a three-way valve, so that a first valve inlet 261 is provided for introducing compressed air and a second valve inlet 262 is provided for discharging compressed air from a pressure zone. A third valve inlet 263, which is fluidly connectable to the first and second valve inlets 261, 262, can, however, supply compressed air from a pump to the pressure zone or discharge it from the pressure zone to an outlet. By means of a spring 141, the valve 26 can be closed in a de-energized state, i.e., assume a blocking state 252. To discharge compressed air, the spring 141 can also be deflected by an electrical actuator 132, so that the valve 26 assumes the open state 251 and discharge of compressed air through the second valve inlet 262 is made possible.

[0181] Figure 11 shows a third embodiment of a patient support 101 in the form of a seat cushion. This third embodiment of the patient support 101 differs from the patient support 101 of Fig. 1 and Fig. 3 in that several fluid cells 3 form different pressure zones 61, 62, 63, 64, 65 in a seating area 1. The respective pressure zones are each marked with a different pattern for better recognition. The fluid cells 3 of a pressure zone 61, 62, 63, 64, 65 are each fluidically connected to one another by lines, so that they can be jointly pressurized with compressed air at a uniform pressure. In addition, the respective pressure zones 61, 62, 63, 64, 65 each have only one common supply from a pump of the patient support 101 to one of the fluid cells 3 of the pressure zone 61, 62, 63, 64, 65. Each of the pressure zones 61, 62, 63, 64, 65 has only one zone valve.

[0182] The fluid cells 3 of two pressure zones 61, 63 are arranged spaced apart from each other in plan view by fluid cells 3 of other pressure zones 62, 64, 65. This arrangement makes it possible, for example, to take into account the often partially mirror-symmetrical seating surface of a patient without having to calibrate pressure zones separately.

Claims

Patent claims 1. Patient support (101), preferably a seat support, comprising a support area (1) with a base (2), a plurality of fluid cells (3) which are arranged on a seat side of the base (2), a pump (4), and a control unit (5), wherein one or more fluid cells (3) each define a pressure zone (6) and each pressure zone (6) is connected to the pump (4) by at least one zone valve (7), wherein each zone valve (7) can be actuated by the control unit (5) so that a pressure in each pressure zone (6) can be set by the control unit (5), characterized in that the patient support (101) comprises at least one pressure sensor (8) for measuring the pressure in at least one pressure zone (6), preferably at least one pressure sensor (8) per pressure zone (6).

2. Patient support (101) according to claim 1, wherein the patient support (101) comprises a sinking sensor (9), wherein the sinking sensor (9) is adapted to detect a sinking depth (91), in particular to detect whether a predefined sinking depth (91) is exceeded.

3. Patient support (101) according to claim 2, wherein the sinking sensor (9) is configured to detect contact between an inner wall section (30) of at least one fluid cell (3) with another element, preferably an opposite inner wall section (31) of the fluid cell (3), the base (2), and / or the sinking sensor (9). Patient support (101) according to one of claims 2 or 3, wherein the sinking sensor (9) comprises two sections (92, 93) which are movable relative to one another at least partially perpendicular to the support region (1) and / or the sinking sensor (9) is designed to be at least partially deformable in a direction perpendicular to the support region (1), and the sinking sensor (9) preferably triggers before a maximum sinking depth (91) is reached. Patient support (101) according to one of the preceding claims, wherein the patient support (101) is a seat support and is designed for use on a wheelchair (102) and in particular has a maximum extension in plan view of a maximum of 65 cm, preferably a maximum of 55 cm.Patient support (101) according to one of the preceding claims, wherein the patient support (101) has a thickness (D) perpendicular to the support area (1) in a range from 4 cm to 20 cm, in particular a thickness (D) in a range from 4 cm to 15 cm or from 4 cm to 10 cm. Patient support (101) according to one of the preceding claims, wherein at least one pressure zone (6) has a different shape or surface than another pressure zone (6), in particular in a plan view of the patient support (101). Patient support (101) according to one of the preceding claims, wherein the patient support (101) has an outlet valve. (13) and an inlet valve (12), wherein the inlet valve (12) is fluidly connected to the pump (4) and the outlet valve (13) and inlet valve (12) are fluidly connected to at least one zone valve (7), preferably min- at least two zone valves (7), in particular preferably all zone valves (7). Patient support (101) according to one of the preceding claims, wherein at least one of the group of the inlet valve (12), the outlet valve (13), and the zone valve (7) is closed when de-energized and preferably comprises a check valve (14). Patient support (101) according to one of the preceding claims, wherein the pump (4) and / or an exhaust air silencer (131) has a lower volume than 30 dB, preferably less than 25 dB, particularly preferably less than 20 dB, at a distance of 1 m from the patient support (101). Patient support (101) according to one of the preceding claims, wherein the pump (4) is a diaphragm or ultrasonic pump.Patient support (101) according to one of the preceding claims, comprising an elastic cover (15), wherein the cover (15) is adaptable along a contour (32) of the fluid cells (3) when a force, in particular the weight force (16), of a patient (11) acts on the cover (15) without causing a significant force parallel (17) to the support area (1). Patient support (101) according to one of the preceding claims, wherein the patient support (101) comprises at least one humidity sensor (18) and / or temperature sensor (19) for measuring the humidity and / or temperature on the seat side of the base (2). Patient support (101) according to one of the preceding claims, wherein the patient support (101) comprises a ventilation device (20) for the supply and / or removal of fluid on the seat side of the base (2), wherein the ventilation device (20) is preferably operable by the pump (4). Patient support (101) according to one of the preceding claims, wherein the control unit (5) or an additional computer arrangement of the patient support (101) is designed to detect temporal pressure changes in at least one pressure zone (6) by means of at least one pressure sensor (8) or the sinking sensor (9) and to assign them to an activity pattern.Patient support (101) according to one of the preceding claims, wherein the patient support (101) is operable in at least one first operating mode (21) and one second operating mode (22), wherein the control unit (5) is designed to control the pressurization of the pressure zones (6) such that the first operating mode (21) has a first pressure ratio between at least two pressure zones (6) and the second operating mode (22) has a second pressure ratio between the two pressure zones (6) that is different from the first. Patient support (101) according to claim 16, wherein the control unit (5) is designed such that in the first or second operating mode (21, 22). (i) a temporally repeated pressurisation and depressurisation of at least one pressure zone (6), in particular groups of pressure zones (6), takes place, and / or (ii) an activity pattern of a patient (11) is detected and the pressure zones (6) are pressurised in accordance with this activity pattern, and / or (iii) the pressure zones (6) are pressurised to ensure stable positioning of the patient (11), and / or (iv) the fluid cells (3) are pressurized up to a maximum pressure. Patient support (101) according to one of the preceding claims, wherein the base (2) on the seat side has no fluid cell (3) in a region, in particular a region adjacent to an edge of the base (2), and the control unit (5) and / or the pump (4) are arranged in this region of the base (2). Patient support (101) according to one of the preceding claims, wherein the patient support (101) has a pressure connection (24) with which at least one additional device can be pressurized by the pump (4) if the additional device is connected via the pressure connection (24) is connected to the patient support (101). Patient support (101) according to one of the preceding claims, wherein a pressure relief valve is assigned to at least one fluid cell (3), preferably at least one fluid cell (3) per pressure zone (6). Patient support (101) according to one of the preceding claims, wherein the fluid cells (3) comprise or consist of a plastic, in particular polyurethane, polychloroprene, poly(organo)siloxane, polyisoprene, polyethylene, polypropylene, polystyrene, or polyester. Patient support (101) according to one of the preceding claims, wherein the patient support (101) comprises a wireless communication interface for transmitting status data of the patient support (101) and / or receiving user input data, in particular for selecting the operating mode (21, 22) for operating the patient support (101). Patient support (101) according to one of the preceding claims, wherein the patient support (101) comprises a data memory and a computing unit, wherein at least one target pressure value of at least one pressure zone (6) can be calculated with the computing unit based on at least one measured value of the sinking sensor (9) and / or pressure sensor (8), wherein the measured values ​​and / or the target pressure value can be stored in the data memory, and a pressure in at least one pressure zone (6) can be adjusted by the control unit (5) based on the target pressure value. Wheelchair (102) comprising a patient support (101) according to one of the preceding claims.Method for the automated calibration of a patient support (101), preferably a patient support (101) according to claims 1 to 23, comprising the following steps:. - placing a patient (11) on the patient support (101) so that a weight force (16) is exerted on the patient support (101); - varying a pressure of at least one pressure zone (6) and determining at which pressure a sinking sensor (9) detects a sagging; - Save the measured pressure.

26. Method according to claim 25, wherein when varying the pressure of at least one pressure zone (6), the sinking depth (91) is measured as a function of the pressure.

27. Method according to one of claims 25 or 26, wherein a target pressure value in at least one pressure zone (6) is determined on the basis of the determined pressure of the pressure sensor (8) at which the sinking sensor (9) detects.

28. Method according to one of claims 25 to 27, wherein the sinking sensor (9) is arranged in a pressure zone (6), wherein on the basis of the determined pressure of the pressure sensor (8) at which the sinking sensor (9) detects, the pressure of the pressure zone (6) and at least one adjacent pressure zone (6) is adjusted.

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