Battery modules for wireless exchange of data and power

Abstract

The present invention relates to a battery module, which is used for wirelessly exchanging data and power between the battery module and another device of a system, and the system is particularly a patient monitoring system, and the battery module is coupled to the other device. The battery module comprises: a sealed housing (93); a battery cell (91) for storing electrical energy; a data storage unit (94) for storing data; and a connector (95). The connector comprises a data transmission unit (96) and a magnetic coupling unit (92), the data transmission unit being used to transmit data to another device of the system having a mating connector and / or receiving data from another device of the system having a mating connector, and the magnetic coupling unit being separate from the transmission unit (96) and being used to transmit power to another device of the system having a mating connector and / or receiving power from another device of the system having a mating connector by using inductive coupling. The battery module is configured for mobile use and coupling with different devices of the system.

Description

Technical Field

[0001] The invention relates to a battery module for wirelessly exchanging data and power between the battery module and another device of a system, in particular a patient monitoring system, to which the battery module is coupled. Background Art

[0002] Generally speaking, wireless charging or powering of devices is an established technology that is convenient for users. Wireless powering can also be used in harsh environments, where corrosion or moisture may compromise functionality or safety when using current contacts. There are various standards for wireless powering, such as Qi, PMA, Rezense, WiPower, and the market is developing rapidly. These technologies are mainly used to charge battery-powered devices (e.g., mobile phones, tablets, etc.). Charging of multiple devices is possible. For example, in the Qi standard, power strips with many smaller coils are available, but the devices need to be precisely positioned adjacent to each other (in a horizontal plane).

[0003] High-end patient monitoring is expanding from its traditional applications in intensive care units (ICU, OR) to lower acuity settings such as general wards, hospital-to-home, and related primary care. The success of existing high-end products is attributed to the quality of measurement across the product line, its modularity, overall system connectivity, user interface, and its consistency (backward compatibility). At the same time, the value segment is rapidly expanding to cater to emerging countries and lower acuity settings where low cost is a major consideration. In these markets, compromises may be made on modularity, connectivity, and (sometimes) measurement quality.

[0004] In the area of ​​lifestyle and sports, physiological measurements (eg heart rate, respiratory rate, SpO2) are also increasingly used.

[0005] In the new application spaces described, wearable (cordless) sensors, miniaturization and low power are necessary. The basic requirements for all these segments are the same, namely, excellent measurement quality compared to non-compromised patient electrical safety. Patient electrical safety is strictly regulated by the IEC 60601 standard and indicates a maximum leakage current of 10μA, a ground separation of 4kV and a separation of 1.5kV between each measurement in the worst case (direct connection to the heart). In addition, patient monitors must be able to withstand high differential voltages caused by defibrillators and large RF voltages from surgical blades.

[0006] Conventional isolation and protection concepts are based on inductive power couplers (transformers) and optical data couplers for data transmission, and then maintaining sufficient creepage and clearance between the PCB and the connector pins.

[0007] US 6819013 B2 discloses an electrically isolated combined power and signal coupler for a patient connection device. A docking station and a portable device that can be docked with the docking station both include a power coupler and an electrically isolated data transducer. The respective power couplers include a magnetically permeable element and a printed circuit board, the magnetically permeable element including a center pole and a peripheral pole, the printed circuit board having an opening through which the center pole extends. The printed circuit board includes a winding around the center pole opening, the winding including a primary winding in the docking station and a secondary winding in the portable device. When the portable device is docked with the docking station, the magnetically permeable element in the portable device and the magnetically permeable element in the docking station are arranged to form a magnetic loop, and the data transducer in the portable device and the data transducer in the docking station are arranged to exchange data.

[0008] US 2010 / 312310 A1 discloses a power transmission system for an implantable device such as an implantable medical device. The implantable device and the power transmission device both include a coil having a magnetically conductive core, so that the coil is operatively magnetically coupled to improve the efficiency of power transmission. The coil resides in a conductive implant box.

[0009] US 2015 / 077065 A1 discloses a method and system for recharging a battery-operated device, thereby making the recharging process less onerous and convenient for the user of the device. Embodiments provide for incorporating recharging into a normal mode of use for the device by using activities consistent with the intended use of the device, thereby making the user aware of the inconvenience. Other embodiments provide for systematic detection and wireless charging of the device, thereby reducing or completely eliminating the burden on the user. Summary of the invention

[0010] An object of the present invention is to provide a battery module for wireless exchange of data and power, which can be seamlessly integrated into a system of a device and facilitates the workflow within the system in various scenarios and environments.

[0011] In one aspect of the present invention, a battery module is provided for wirelessly exchanging data and power between the battery module and another device of a system, in particular a patient monitoring system, the battery module being coupled to the other device, the battery module comprising:

[0012] - Sealed housing;

[0013] - battery cells, which are used to store electrical energy;

[0014] - a data storage unit for storing data; and

[0015] - a connector, comprising a data transmission unit and a magnetic coupling unit, the data transmission unit being used to transmit data to another device of the system having a mating connector and / or receiving data from another device of the system having a mating connector, the magnetic coupling unit being separate from the transmission unit and being used to transmit power to another device of the system having a mating connector and / or receiving power from another device of the system having a mating connector by using inductive coupling, wherein the battery module is configured for mobile use and coupling with different devices of the system. And wherein the sealed housing is configured to allow the battery module to be stacked onto other devices having a mating connector

[0016] Preferred embodiments of the invention are defined in the dependent claims.

[0017] Wireless measurements, for example in clinical settings, are generally becoming more and more important, which require the use of batteries. The present invention solves at least some of the drawbacks of using batteries, for example in clinical settings. These drawbacks include reliability issues with battery contacts (especially for medical devices) in terms of contact resistance, hygiene (edge ​​cleaning) and electrical safety. In addition, battery management interferes with clinical workflows by requiring different charging stations and connectors for each of the batteries used. This is considered to be one reason why wireless measurements are not currently widely used in clinical settings. The presence of contacts also complicates battery replacement / replacement, especially for body-worn sensors. Batteries (especially lithium-ion and lithium-polymer batteries) need to be handled carefully to avoid mechanical damage. Batteries integrated into measurement modules also have serious drawbacks: namely, the size of the measurement module depends on the battery capacity implemented, so there are modules of different sizes for the same measurement, these measurement modules need to be replaced when the battery is empty, and measurements need to be scheduled or redone when the battery's life expires. Finally, there is currently a failure to integrate battery management into the clinical workflow on a health continuum, which may introduce safety issues due to "unhealthy" batteries.

[0018] The present invention is based on the concept of coupling a battery cell sealed in a housing, preferably with a smooth surface and without edges, to other devices via a contactless interface technology. The contactless interface technology is configured for bidirectional exchange of power and data. It specifically includes a device for charging the battery cell and delivering the charged energy to other devices via contactless magnetic coupling. In addition, it includes a device for receiving data (e.g., sensor data collected by a sensor and delivered to a measurement module) and storing the data on a data storage device (e.g., a semiconductor storage unit) and transmitting the stored data to another device (e.g., such as a central processing unit of a patient monitor) for further processing.

[0019] Bidirectional power transfer can be achieved through two fully-fledged unidirectional magnetic power supply channels (e.g., unidirectional magnetic power supply channels standardized in the Qi standard or the PowerMat standard). This requires four coils (two transmit coils and two receive coils). In another embodiment, two sets of unidirectional magnetic power supply channels multiplexed to two coils can be used. Still further, one set of bidirectional magnetic power supply channels (two transmit / receive coils) can be used by using, for example, a dedicated H-bridge for both AC power generation and rectification.

[0020] The advantage of the proposed method is that the contactless power transmission avoids the need for galvanic contacts. The sealed housing (e.g., sealed box) is robust, well protected and fluid-tight and preferably has no edges and grooves. The battery module is thus easy to clean and easy to replace. In addition, due to the common interface connection with other devices of the system through magnetic coupling, i.e., all devices preferably use the same (mechanical and electrical (i.e., magnetic and data transmission)) interface, an easy workflow can be installed.

[0021] In addition, the battery cell is scalable not only in terms of capacity and / or size, i.e. in terms of volume, but also in terms of battery technology (newer batteries have higher capacity in the same volume). The size of the measurement module or other device remains independent of the battery capacity, even though the thickness may change the interface and the connection interface remains fixed. This enables the use of very thin body-worn measurement modules (e.g. patch-like measurement modules). Due to the use of the proposed connection interface, battery management can be seamlessly integrated into the architecture of the system and the clinical workflow is facilitated. Finally, the safety of the system is improved by not drawing unwanted currents from the battery, because smart safety measures can be implemented in the system (e.g. patient network) (e.g. via contactless data transmission) using items such as: identifier, charge status, remaining measurement time for a specific measurement, battery status, temperature, current, history, etc.

[0022] In an embodiment, the battery unit further comprises a second connector (which is preferably configured in the same manner as the first connector and which may form a common connection interface with the first connector), the second connector being used to simultaneously send data to and / or receive data from two other devices of the system, and / or to simultaneously send power to and / or receive power from two other devices of the system. Thus, simultaneous bidirectional exchange of data and / or power is possible. However, it should be noted that data may be communicated (e.g. via a short-range radio link) even in the absence of a mating connector and in the absence of power being transmitted. In addition, more than two connectors may be provided, depending on the actual stacking geometry.

[0023] The battery unit may comprise a rechargeable battery or a capacitor, in particular a supercapacitor. Generally, any rechargeable technology (NiCd, Li-ion, Li-polymer, etc.) can be used. Supercapacitors are worth considering, as they may be quickly charged, for example during a temporary connection to a readout unit for spot checks on a general ward.

[0024] The battery cell may also include a sensor unit including a temperature sensor, a voltage sensor, and / or a current sensor. Sensing voltage and / or current may be used to determine the state of charge of the battery cell and the expected time to empty. Sensing temperature may improve safety; for example, charging may be stopped if the temperature is too high.

[0025] In another embodiment, the battery module may further include a processing unit for performing data processing, time counting, self-diagnosis and safety on the received data. This enables management of battery quality, such as predicting the time to replace a battery cell with a new one.

[0026] The processing unit may be configured to calculate the expected operating time when applied to a measurement module. When a battery is powering one or more measurement modules, it is important for clinical workflow (especially for patient safety) and battery management to know how long the battery has been used before it needs to be recharged or replaced or before a cable should be attached. This can be achieved by this embodiment.

[0027] In a preferred embodiment, the battery module also includes: a detection unit, which is used to detect the strength of the magnetic coupling between the magnetic coupling unit and the magnetic coupling unit of another device, and a control unit, which is used to switch the data sending unit to a low power mode and / or enable the magnetic coupling unit when the detected magnetic coupling is higher than a first threshold and / or the detected increase in magnetic coupling is higher than a second threshold, and switch the data sending unit to a high power mode and / or disable the magnetic coupling unit when the detected magnetic coupling is lower than a third threshold and / or the detected decrease in magnetic coupling is higher than a fourth threshold.

[0028] This embodiment is based on the idea of ​​utilizing a connector technology that can operate in two modes, namely a near-field mode and a far-field mode. When the connector of the battery module is mechanically connected to the mating connector of another device, the near-field mode is used, in which the radio (i.e., the data transmission unit) switches to a low-power mode, enables magnetic power transfer, and shields the RF radiation and magnetic field from the measurement electronics and the outside world. When not connected, the far-field mode is used, in which the radio switches to a high-power mode to enable short-range radio communication and disable magnetic power transfer. In order to control the switching between the two modes, the magnetic coupling and / or its increase or decrease is detected between the detector and the potential mating connector. The switching between the different modes is then determined using a predetermined threshold for the magnetic coupling and / or its increase / decrease.

[0029] In another embodiment, the data transmission unit is configured to transmit the data by using RF transmission, optical transmission, capacitive coupling or near field communication.

[0030] Preferably, the connector further comprises a carrier, wherein the data transmission unit comprises an RF antenna and an RF circuit, the RF wire being arranged in or on the carrier, and the RF circuit being used to drive the RF antenna and / or obtain an RF signal received by the RF antenna. Various designs of the RF antenna are generally possible. Preferred antenna designs include the RF antenna being shaped in the form of a strip, a ring, a planar inverted F-type or a planar folded dipole. In addition, the RF antenna is preferably arranged to be rotationally symmetrical, which avoids a predetermined rotational positioning of the connector relative to the mating connector when they are connected. In an exemplary implementation, a quarter-wavelength planar inverted F-type antenna can be used.

[0031] In another embodiment, the magnetic coupling unit comprises a flux concentrator and one or more coils, the flux concentrator being used to gather the magnetic flux, the one or more coils being arranged around a portion of the flux concentrator. Therefore, inductive coupling like a transformer is preferred for power transmission. Other reasons are efficient power transfer, low stray flux (which can interfere with sensitive measurements or other sensitive equipment, such as pacemakers).

[0032] The sealed housing is configured to allow the battery module to be stacked onto other devices having a mating connector. Preferably, the magnetic coupling unit comprises:

[0033] a (e.g. annular or rotationally symmetrical) flux concentrator which at least partially has a U-shaped cross section, forming a recess between the legs of the U,

[0034] - a first coil arranged in a recess of said flux concentrator, and

[0035] - a second coil arranged outside the recess in which the first coil is arranged,

[0036] In which, the sealed shell is arranged to allow the battery module to be stacked onto other equipment with a matching connector, so that the first coil of the connector together with the second coil of the connector stacked onto the connector forms a first transformer for inductive power transmission between the two, and / or the second coil of the connector together with the first coil of the third connector stacked onto the connector forms a second transformer for inductive power transmission between the two.

[0037] This embodiment is based on the idea of ​​providing a modular approach to wirelessly powered devices (including the battery module) such that multiple devices can be stacked on top of each other. The flux concentrator (e.g., a core used in a transformer), the coil, and especially the housing are configured such that two or more of the connectors can be easily stacked together to achieve the desired wireless coupling, thereby performing cordless power transfer (and optionally also wireless data transfer) between the stacked connectors.

[0038] When stacked, the upper coil (i.e., the first coil) and the lower coil (i.e., the second coil) are both surrounded by the same high magnetic permeability material of the portion of the flux concentrator of the stacked connector, i.e., these portions of the two flux concentrators form a closed magnetic loop. This allows the two coils to be tightly magnetically coupled. According to an embodiment, a protrusion may be formed in the housing that fits into a recess of the stacked connector, which allows the connectors to be easily stacked.

[0039] There are generally two possible arrangements for the coils of the flux concentrator and the connector. In one arrangement, the coils are arranged on top of each other in the vertical direction, and in the other arrangement, the coils are arranged one relative to the other in the lateral direction. The main advantages achieved by the common approach forming the basis of these two arrangements of the proposed stackable connector are flexibility and the absence of galvanic contacts, thereby providing sufficient reliability and enabling easy cleaning and electrical isolation between devices having such a connector.

[0040] The housing can be configured as a plastic sealed box of the size of a circularly symmetrical disk. Thus, the circularly symmetrical geometry includes polygons (triangles, squares, etc.), and ultimately a disk of circular shape. The flux concentrator can be an inverted U-shaped flux concentrator made of a high permeability material. Preferably, the flux concentrator has a low permeability for RF, or the walls can be coated with a conductive material to shield and guide the RF field. A power control device can be provided to exchange energy with the coil. An RF antenna and a radio device can be provided to enable wireless data transmission.

[0041] In another embodiment, the data transmission unit can be configured to communicate battery identification, battery status (charge), battery health, and battery history within a system (e.g., a patient network) and can be used to manage the battery module, such as calculating the expected operating time when applied to the measurement module. Battery health depends on its usage history. Therefore, it is useful to know the reliability of the battery and the expected time that the battery can be used, such as to replace the battery in a good time. There can be two options for communicating information about battery health and battery history, including: a) self-diagnosis by the battery unit based on temperature, charge and discharge curves, and communicating this self-diagnosis; and b) communicating raw data to enable decision and diagnosis of the central power station (network). BRIEF DESCRIPTION OF THE DRAWINGS

[0042] These and other aspects of the invention will become apparent and elucidated with reference to the embodiment(s) described hereinafter. In the following drawings:

[0043] Figure 1 A schematic diagram of a known system comprising a plurality of devices is shown,

[0044] Figure 2 A schematic diagram showing a first embodiment of a system including a plurality of devices according to the present invention is shown,

[0045] Figure 3 A first embodiment of a connector for use in a system according to the invention is schematically shown,

[0046] Figure 4 A second embodiment of a connector for use in a system according to the invention is schematically shown,

[0047] Figure 5 A third embodiment of a connector for use in a system according to the invention is schematically shown,

[0048] Figure 6 A fourth embodiment of a connector for use in a system according to the invention is schematically shown,

[0049] Figure 7 A fifth embodiment of a connector for use in a system according to the invention is schematically shown,

[0050] Figure 8 shows a schematic diagram of a second embodiment of a system according to the invention,

[0051] Fig. 9 shows a schematic diagram of a third embodiment of a system according to the invention,

[0052] Fig. 10A and Fig. 10BSchematically showing a cross-sectional view and a top view, respectively, of a sixth embodiment of a connector for use in a system according to the invention,

[0053] Fig. 10C A sixth embodiment of a connector for use in a system according to the invention is schematically shown in a connected state, the connector being connected to a counterpart connector,

[0054] Fig.11 Schematically shows a seventh embodiment of a connector for use in a system according to the invention,

[0055] Fig. 12A and Fig. 12B Schematically showing a cross-sectional view and a top view, respectively, of an eighth embodiment of a connector for use in a system according to the invention,

[0056] Fig.13A and Fig. 13B Schematically showing a cross-sectional view and a top view, respectively, of a ninth embodiment of a connector for use in a system according to the invention,

[0057] Fig.14A and Fig. 14B Schematically showing a cross-sectional view and a top view, respectively, of a tenth embodiment of a connector for use in a system according to the invention,

[0058] Fig.15 schematically shows an eleventh embodiment of a connector for use in a system according to the invention,

[0059] Fig.16 Schematically showing the layout of the connector with automatic switching between modes,

[0060] Fig.17A , Fig. 17B , Fig. 17C and Fig.17D Schematically showing a cross-sectional view, a top view, and a first perspective view and a second perspective view, respectively, of a first embodiment of a stackable connector for use in a system according to the present invention,

[0061] Fig.18A , Fig.18B and Fig.18C schematically showing a cross-sectional view and a first perspective view and a second perspective view, respectively, of a stack of two connectors according to a first embodiment,

[0062] Fig.19 schematically shows a stack of three connectors according to a first embodiment,

[0063] Fig. 20A , Fig. 20B and Fig. 20Cschematically shows an arrangement of several devices in a daisy chain, each device comprising one or more of the connectors according to the invention,

[0064] Fig.21A and Fig.21B Schematically showing a cross-sectional view and a top view, respectively, of a second embodiment of a stackable connector for use in a system according to the present invention,

[0065] Fig.22A and Fig. 22B Schematically showing a cross-sectional view and a top view, respectively, of a third embodiment of a stackable connector for use in a system according to the present invention,

[0066] Fig.23A , Fig. 23B and Fig.23C Schematically showing a cross-sectional view, a top view and a simplified cross-sectional view of a fourth embodiment of a stackable connector for use in a system according to the present invention, respectively,

[0067] Fig.24 Schematically shows a fifth embodiment of a stackable connector for use in a system according to the invention,

[0068] Fig.25A and Fig.25B Schematically showing a cross-sectional view and a top view, respectively, of a sixth embodiment of a stackable connector for use in a system according to the present invention,

[0069] Fig.26A and Fig.26B Schematically showing a cross-sectional view and a top view, respectively, of an embodiment of a connector with a transverse geometry for use in a system according to the invention,

[0070] Fig.27A and Fig.27B The following schematically shows the use of Fig.26A and Fig.26B A cross-sectional view and a top view of a daisy chain of connectors are shown.

[0071] Fig.28A and Fig.28B The following schematically shows the use of Fig.26A and Fig.26B A cross-sectional view and a top view of a body-worn sensor arrangement of the connector shown,

[0072] Fig.29 The schematic diagram shows the use of Fig.26A and Fig.26B The connectors shown couple the various modules and units to the patient monitor.

[0073] Fig.30A schematic diagram showing a fourth embodiment of a system according to the present invention is shown, the system comprising a battery module,

[0074] Fig.31 shows the overall layout of the cable unit according to the present invention,

[0075] Fig.32 Diagram showing the use of cable units in high acuity environments.

[0076] Fig.33 The diagram shows the use of the cable unit in a lower acuity environment.

[0077] Fig.34 A schematic diagram showing a fifth embodiment of a system according to the present invention is shown, the system comprising a storage module,

[0078] Fig.35 A schematic diagram showing an embodiment of a battery module according to the present invention is shown,

[0079] Fig.36 A schematic diagram of an embodiment of a cable unit according to the present invention is shown, and

[0080] Fig.37 A schematic diagram showing another embodiment of a device according to the present invention is shown, the device applying a pairing method. DETAILED DESCRIPTION

[0081] Figure 1 A schematic diagram of a known system 1 is shown comprising a plurality of devices 2, 3, 4, 5 configured to transmit power and data between them. Conventionally, a modular approach is used, according to which measurement modules 3, 4 (representing one type of device) are connected to a central processing unit 2 (representing another type of device), such as a central processor on a motherboard of a patient monitor, via expensive gold-plated motherboard connectors (i.e., via galvanic connections) 8. Additionally, an isolated measurement module 5 (representing another type of device) on the motherboard may be connected to the main processing unit 2 in the same manner.

[0082] Some measurements may be implemented directly on the mainboard itself. The measurements are isolated from each other, for example by using optocouplers 6 for data transmission and transformers 7 for power transmission. All metal parts share the same (protected) ground connection; the measurements themselves are isolated from ground. Each measurement module 3, 4, 5 may be connected, typically via a cable, to one or more sensors (not shown) placed on the patient's body, for example, a pulse oximetry sensor, an accelerometer, ECG electrodes.

[0083] In such systems, electrical isolation involves a large part (at least 30%) of the measurement costs. In addition, the motherboard connectors are expensive and mechanically complex, and cleaning is a challenge. Reducing costs is a strong requirement in the value segment and lower acuity environments. Modularity is a strong requirement in the high-end market and to a lesser extent in the lower acuity and value segments. Wearable (untethered) sensors and low power are very important for low acuity care environments. In addition, aligning the measurement concept across the company's product range can reduce costs and maintain the same quality for all market segments.

[0084] Therefore, there is a strong need for a low-cost, low-power, flexible and modular architecture that is universally applicable to all patient monitoring environments, or more generally to all systems comprising multiple (different and / or identical) devices where power and / or data need to be transmitted under some or all of the above constraints.

[0085] Figure 2 A schematic diagram of a first embodiment of a system 10 comprising a plurality of devices 20, 30, 40, 50 according to the present invention is shown. According to this embodiment, the devices 30, 40, 50 (e.g., representing measurement modules 30, 40, 50) are all wirelessly connected to a central processing unit 20, such as a patient monitor. For example, the measurement modules in a patient monitoring system are connected to the central processing unit 20 via individual magnetic coupling power transmission and near-field contactless data transmission (thereby there may also be devices that are only provided for magnetic coupling power transmission or near-field contactless data transmission). This flexible architecture is consistent with the following physiological measurement applications: measurement modules located on the mainboard (i.e., in the central processing unit 10), modular "plug-in" measurement modules, measurement modules located in a mobile measurement server connected to the central processing unit 10, and cordless measurement modules. Typically, such measurement modules are electrically insulated from each other. The measurement modules can also be combined in a single mechanical housing, and they can be completely electrically insulated via their own coils.

[0086] The magnetic power coupling may for example be integrated in a track of a (motherboard) PCB or implemented as a magnetic coil in each of two different parts of a connector for connecting two devices.

[0087] The contactless data transmission between the two devices is preferably realized via near field communication means, such as Bluetooth 4.0 (low energy), Wi-Fi, ZigBee, capacitive (e.g. parasitic capacitance via magnetic coupling) or optical means, wherein radio transmission is the preferred option. Preferably, a (e.g. standardized) radio protocol is used to comply with all four mentioned applications, such as BLE, which is already integrated in many commercial off-the-shelf (COTS) components. Basically, any unregulated radio protocol can be used in case the radiated field is confined to a certain volume (e.g. inside the housing of the monitor).

[0088] Typically, each device capable of transmitting data and power in a wireless manner comprises: a housing; a magnetic coupling unit arranged within the housing for transmitting power to another device of the system having a mating connector and / or receiving power from another device of the system having a mating connector by using inductive coupling; and a data transmitting unit arranged for transmitting data to another device of the system having a mating connector and / or receiving data from another device of the system having a mating connector, in particular by using RF transmission, optical transmission, capacitive coupling or near field communication.

[0089] The measuring modules 30, 40 each comprise a housing 31, 41, a magnetic coupling unit 32, 42 and a data transmission unit 33, 43. In addition, each of them comprises a patient-side connection unit (PSC) 34, 44 for connecting the respective measuring module 30, 40 to a sensor or electrode (not shown) (usually in a galvanic manner) in order to receive data signals from the sensor or electrode and / or to send control signals to the sensor or electrode. Optionally, additional devices for analog processing and / or digital processing can be provided, and the measuring module can contain a small energy buffer (e.g., a battery or supercapacitor) to bridge the conversion time between wired-wireless scenarios and to bridge the conversion time during battery replacement.

[0090] The isolated measurement module 50 (ie, the measurement module integrated on the main board of the patient monitoring device) includes a housing 51, a magnetic coupling unit 52, and a data transmission unit 53. In addition, the isolated measurement module 50 also includes a patient side connection unit (PSC) 54.

[0091] The central processing unit 20 comprises a housing 21, several magnetic coupling units 22, 22a, 22c and several data transmission units 23, 23a, 23b, which may also be combined into a single data transmission unit, wherein the magnetic coupling units and the data coupling units form a connection module for connecting an (external) device to the central processing unit 20. In addition, the central processing unit 20 comprises power supply terminals 24, which comprise an isolation barrier for coupling the central processing unit 20 to an external power supply 60. Furthermore, the central processing unit 20 typically contains all the hardware required for power and voltage generation, control, input / output, display and central processing of data from measurements and alarm generation.

[0092] The ability to send data and power between two devices of the system 10 is indicated by blocks 61, 62, 63. It should be noted that the system 10 may also include devices that are not configured to send and receive data and power, but are configured to only send data and / or power, or configured to only receive data and / or power.

[0093] exist Figure 3 A first embodiment of a connector 100, 110 for wirelessly transmitting data and / or power between separate devices comprising such a connector is schematically shown in a top view in FIG. These connectors 100 (e.g., a connector of a central processing unit) and 110 (e.g., a connector of a measurement module) represent a low-cost solution and can be implemented on a board. The tracks of the PCB 102, 112 can be used as transformer windings (i.e., coils) 101 (e.g., representing a primary coil), 111 (e.g., representing a secondary coil) separated in the horizontal direction and / or vertical direction. The magnetic coupling can be enhanced by adding a flux concentrator 103, for example, a ferromagnetic core with two legs (each carrying one of the coils 101, 111) and two yokes connecting the two legs to form a ring (which does not necessarily have to be circular, but can also have other shapes, such as rectangular, elliptical, etc.). RF antennas 104, 114 are also integrated on the PCB 102, 112, and the gap 105 between the connectors 100, 110 provides an isolation barrier. The mainboard processor 106 may be provided in a central processing unit, and the measurement unit 116 may be provided on a measurement module.

[0094] Figure 4 Schematically shows a cross-sectional view of a second embodiment of a connector 120, 130 for use in a system according to the invention, which connector 120, 130 provides isolated measurements on a motherboard of a central processing unit. Coils 101, 111 are located on different surfaces of respective PCBs 102, 112 and are magnetically coupled via a flux concentrator 103.

[0095] Obviously, many variations of this approach are possible. Figure 5 A cross-sectional view of a third embodiment of a connector 140, 150 for use in a system according to the invention is schematically shown. In this embodiment, a third intermediate layer 107 is provided in the vertical direction at a height level between the coils 101 and 111, which is arranged within the PCB 102. The third intermediate layer 107 is grounded to reduce stray capacitive coupling between the coils 101, 111. For EMC reasons, additional layers may be added, for example another ground layer 108, such as Figure 6 As shown, Figure 6 A fourth embodiment of a connector 160, 170 for use in a system according to the invention is depicted.

[0096] Figure 7 A cross-sectional view of a fifth embodiment of a connector 180 , 190 for use in a system according to the invention is schematically shown. In this embodiment, a measurement PCB 112 is located on top of a main PCB 102 with an insulating foil 109 in between and is magnetically coupled via a flux concentrator 103 .

[0097] In a further variant of one of the above described embodiments, the secondary coil may be integrated on a chip or in a package of an ASIC comprising the measuring electronic circuit.

[0098] Preferably, the main microprocessor on the central processing unit controls or drives the primary coil of the transformer. The AC voltage of the secondary coil is rectified and stabilized to supply to the measurement module. This approach can use wireless charging of the Qi standard (or other standards), and can generally make the arrangement and construction of components meet the requirements of one or more of these standards (for example, the coil should be close to the surface).

[0099] For data communication, the central processing unit may include a near field radio stack, communicating with the isolated measurement via Bluetooth Low Energy, ZigBee or in any other suitable way. In case radiation is limited to a limited premises, every non-standard protocol is allowed.

[0100] RF transmission can be achieved via a separate antenna, via capacitive coupling pads or even via the parasitic capacitance of the transformer coil. The parasitic capacitance should be kept very small to comply with the IEC 60601-2-49 standard isolation requirements, but this limit is achievable in transmissions in the UHF radio band at 2.4 GHz or higher frequencies, for example.

[0101] Figure 8A schematic diagram of a second embodiment of a system 11 according to the invention comprising a plurality of devices 20, 30, 40 is shown. In this embodiment, one or more measuring modules 30, 40 are adapted, for example, in a measuring stand 20' and are coupled to a central processing unit 20 via magnetic connectors 25, 35 (for module 30) and 26, 46 (for module 40), comprising a primary coil 101 of the central processing unit 20 in close proximity to a secondary coil 111 of the module 30, 40 and an RF antenna 114. For data transmission, an RF antenna 104 may be provided in the central processing unit 20 and a corresponding RF antenna 114 may be provided in the measuring modules 30, 50 (e.g., an antenna for bridging small distances in near field mode, e.g., BT, ZigBee, etc.).

[0102] Cleaning is easy due to the absence of pins. Therefore, these connectors 25, 35, 26, 46 replace the Figure 1 The conventionally used expensive and bulky cleanable current connectors shown. In addition, a PSC unit 34, 44 may be provided for connection to a respective sensor, for example a temperature sensor or a SpO2 sensor.

[0103] The system may further comprise a user interface 70 coupled to the central processing unit 20 , the user interface 70 comprising, for example, one or more displays, buttons, switches, etc. Additionally, a grid power transformer 71 may be provided for connection to the grid power source 60 .

[0104] The measurement can be located inside a removable small box (not shown) (also referred to as a measurement server) close to the patient, which is connected to the patient monitor via a cable including a connector disclosed herein or via a wireless link, so that the measurement server can operate in a hybrid mode (i.e., wired or wireless). In such a measurement server, the battery of each measurement will be charged during normal use. Whenever the patient needs to be moved, the link to the patient monitor may be lost for a certain amount of time; despite this, the individual measurements will continue to measure, record and process all vital signs. Therefore, important data about the patient's health status will not be lost. Again, near the patient monitor, the data may be synchronized with the central server again.

[0105] like Fig. 9 , shows another embodiment of a system 12 according to the invention, autonomous operation of the measuring modules is possible by placing additional rechargeable batteries 37, 47 in the measuring modules 30, 40. When refitted into the measuring stand, the batteries are charged via magnetic couplings. The batteries are managed at the measuring modules and can (optionally, but not preferably) be charged wirelessly according to the Qi standard.

[0106] Data transmission preferably complies with existing connectivity standards. For example, when using a Bluetooth LE 4.0 radio, the patient monitor will be directly applicable to the Continua Health Alliance, a non-profit open industry organization in which health care and technology companies work together to improve the quality of personal health care. The Continua Health Alliance is committed to building an interoperable system of personal connected health solutions and extending these solutions to the home, promoting individual independence and providing opportunities for truly personalized health and wellness management. These goals are supported by the present invention.

[0107] Figure 10 to Fig.15 Further embodiments of the connector according to the invention are shown.

[0108] FIG. 10 schematically shows a cross-sectional view of a sixth embodiment of a connector 200 in an unconnected state for use in a system according to the present invention ( Fig. 10A ) and top view ( Fig. 10B ). The connector 200 includes a PCB 202, which includes a quarter-wavelength planar inverted F antenna (PIFA) 204 as part of a data transmission unit integrated in the track 290. The RF antenna 204 is formed by an RF signal line 205 and a ground plane 206. The magnetic field is generated by coils 201a, 201b wrapped around a C-shaped (also called U-shaped) flux concentrator 203, which is made of a material with high magnetic permeability for the frequencies of interest. Additional conductive sheet material (as a covering) can be added to shorten the remaining stray fields in the electronic device through eddy currents. Additional cladding of the core 203 can help shield the RF signal as a short-range radio field 209. When no other connectors are attached (i.e., in an unconnected state), the RF antenna 204 operates in a far-field mode, in which its directivity is as shown in FIG. Fig. 10A The shown direction is toward the outside.

[0109] The power unit 207 is coupled to the coil 201 for supplying power to the coil 201 and / or receiving power from the coil 201. The RF unit 208 is coupled to the RF antenna 204 for supplying data to the RF antenna 204 and / or receiving data from the RF antenna 204.

[0110] In the connected state, Fig. 10C As shown, connector 200 is shown coupled to mating connector 210, with the poles of both C-shaped flux concentrators 203, 213 and antennas 204, 214 almost perfectly aligned so that RF and magnetic fields are optimally coupled and shielded from the outside.

[0111] The connection triggers two effects:

[0112] i) First, the magnetic coupling increases dramatically, e.g. from k=0.5 to k>0.95, which can be detected directly (e.g. via induced voltage) or indirectly (e.g. using proximity detection). The magnetic powering electronics (e.g. Qi, PowerMat or custom) recognize this effect via a polling mechanism, via changed coil impedance, resonant frequency or induced voltage. In the unconnected state, magnetic powering is disabled, so no interference is caused to the radio channel or measurements. In the connected state, the flux is well confined in the flux concentrators 203, 213, which also prevent interference. Disconnection can be detected by polling the opposite effect (by simply turning off the coil and observing the resulting effect).

[0113] ii) Secondly, since the distance between the two antennas 204, 214 is very short, the amplitude and SNR of the received RF signal is significantly increased. The radio transmitter is now able to smoothly switch to near field mode by reducing its output power while maintaining consistent data communication. As a result, the radiated RF power in the vicinity is significantly reduced, which helps to free up the radio spectrum. In addition, the power consumption of the radio is reduced due to the efficient RF coupling.

[0114] It should be noted that RF coupling in the near field mode is more due to capacitive coupling than to far field EM waves, where the distance is a fraction of the wavelength. Both effects are verified periodically via a polling mechanism, or triggered by additional proximity detection (optical, magnetic) or by a simple mechanical switch or reed switch.

[0115] To avoid stray flux, the coil is preferably not fully (continuously) powered in the absence of a counter-core. However, a polling mechanism can generate power for a short time (e.g., 10 milliseconds) every second to measure the magnetic coupling.

[0116] RF communication and / or data transmission via magnetic coupling (eg, as implemented in the Qi standard) or optical coupling is used to update and negotiate ID, required power, signal quality, charging status, etc. before deciding to begin nominal power transfer.

[0117] The following describes in more detail how the actual connect / disconnect process triggers association in the patient network and how security is implemented.

[0118] Galvanic isolation is ensured by the PCB layer material and the C-core. Alternatively, an additional isolation layer on top of the PCB 202, 212 and the pole tips of the C-core 203, 213 can be added. Unoccupied areas of the PCB can be used for measurement electronics and PSC. Ferrite cores can be good conductors, but there are also high resistance (composite) ferrites available.

[0119] Alternative antenna configurations are possible, such as Fig.11The loop antenna 224 shown, Fig.11 A top view of a seventh embodiment of a connector 220 for use in a system according to the present invention is depicted.

[0120] In Figure 10 and Fig.11 In the illustrated embodiment, the mechanical alignment of the connectors 200, 210, 220 is limited to two rotational orientations where the antenna and C-core are aligned. This is a serious drawback when using cables in body-worn measurements and daisy-chain configurations. This problem is solved by a rotationally symmetric connector 230 as shown in FIG. 12, Fig. 12A and Fig. 12B A cross-sectional view of an eighth embodiment of a connector 230 for use in a system according to the present invention is shown. Fig. 12A ) and top view ( Fig. 12B ).

[0121] The inner leg 232 of the E-core 231 (i.e., a core having a cross section forming an E) carries the coil winding 201 for magnetic power supply. The RF antenna 204 is arranged between the inner leg 232 and the outer leg 233 in the PCB 201 (in practice, as shown in FIG. Fig. 12B Single ring shown). Legs 232, 233 are connected by yoke 236. The inner or outer wall of core 231 can also be coated with conductive material to further reduce interference. When two such connectors are connected, the two halves form a pot-shaped core where magnetic fields and radio signals are well coupled and shielded. In addition, a measurement unit 234 and a PCS unit 235 can be provided.

[0122] Alternatively, the RF antenna 204 is located outside the magnetic core 231, i.e. around the outer leg 233, which may contribute to less crosstalk and interference between the RF signal and the magnetic signal. This is illustrated in FIG. 13, which shows a cross-sectional view of a ninth embodiment of a connector 240 for use in a system according to the present invention ( Fig.13A ) and top view ( Fig. 13B ).

[0123] FIG. 14 shows a cross-sectional view of a tenth embodiment of a connector 250 for use in a system according to the present invention ( Fig.14A ) and top view ( Fig. 14B ), the connector comprises a rotationally symmetrical C-core 251 forming a ring with a C-shaped cross section formed by two legs 252, 253 connected by a yoke 254. The magnetic flux generated by the coil 201 is indicated by arrows 255. The RF antenna 204 is arranged between the inner legs 252 of the C-core 251.

[0124] Fig.15A cross-sectional view of an eleventh embodiment of a connector 260 for use in a system according to the present invention is shown, which is similar to the tenth embodiment shown in FIG. 14 , but in which the RF antenna 204 is arranged around the outer leg 252 of the C-core 251 .

[0125] Figure 10 to Fig.15 The connectors shown offer the advantage that they are rotationally symmetrical and that, in the connected state, there is a very small gap between the connector and its mating connector.

[0126] Fig.16 A connector 270 for wirelessly transmitting data and / or power between separate devices including such a connector is schematically depicted (e.g., FIGS. 10 to 11 ). Fig.15 The connector 270 includes a data transmission unit 271 (e.g., including an RF antenna 204), which is arranged to preferably send data to another device of the system with a mating connector and / or receive data from another device of the system with a mating connector by using RF transmission. The connector also includes a magnetic coupling unit 272 (e.g., including a coil 201 and a core 203), which is used to send power to another device of the system with a mating connector by using inductive coupling and / or receive power from another device of the system with a mating connector. A detection unit 273 (e.g., including a power unit 207) is provided for detecting the strength of the magnetic coupling between the magnetic coupling unit 272 and the magnetic coupling unit of the mating connector. If the detected magnetic coupling is higher than a first threshold and / or the detected increase in magnetic coupling is higher than a second threshold, the control unit 274 switches the data transmission unit 201 into a low power mode and / or enables the magnetic coupling unit 272. In addition, if the detected magnetic coupling is below a third threshold and / or the detected decrease in magnetic coupling is above a fourth threshold, the control unit 274 switches the data transmission unit 271 into a high power mode and / or disables the magnetic coupling unit 272. The thresholds may be predetermined, for example, derived from simulations or from measurements. This embodiment enables the correct mode of the connector to be automatically set, which in particular minimizes power consumption, crosstalk, and use of RF bandwidth.

[0127] It should be noted that Fig.16 The detection unit 273 and the control unit 274 disclosed in the specification can generally be used in all other connectors disclosed herein.

[0128] 17 to 28 show a plurality of embodiments of a stackable connector according to the present invention for explaining details of the stackable connector.

[0129] FIG. 17 schematically shows a first embodiment of a single stackable connector 300 for use in a system according to the present invention, wherein: Fig.17A shows a cross-sectional view, Fig. 17B shows a top view, Fig. 17C A first perspective view is shown, and Fig.17D FIG. 18 schematically shows two stackable connectors 300, 300a of the type shown in FIG. 17 stacked on top of each other, wherein: Fig.18A shows a cross-sectional view, Fig.18B A first perspective view is shown, and Fig.18C A second perspective view is shown. The connector 300 comprises a housing 301 and a magnetic coupling unit 302 arranged in the housing 301, the magnetic coupling unit 302 being used to send power to another device of the system having a mating connector and / or receive power from another device of the system having a mating connector by using inductive coupling. The magnetic coupling unit 302 comprises a flux concentrator 303 (preferably rotationally symmetrical, for example, annular, and made of a high magnetic permeability material), which at least partially has a U-shaped (or C-shaped) cross-section, forming a recess 304 between the legs of the U. A first coil 305 is arranged in the recess 304 of the flux concentrator 303. A second coil 306 is arranged opposite to the first coil 305 and outside the recess 304 in which the first coil 305 is arranged. The flux concentrator 303 may be one of the following different possible forms: for example, an annular form, a circularly symmetrical form, a square form, a triangular form, a rectangular form, etc.

[0130] In addition, a ring RF antenna 307 (as part of a data transmission unit) arranged inside the flux concentrator, an RF unit 308 (including radio electronics), a power unit 309 (e.g., magnetic power electronics), and a measuring unit 310 may be provided in or on a PCB 312. In the second connector 300a, a battery 311 is provided instead of the measuring unit 310. In addition, a PSC unit 313 may be provided in the connector, such as Fig.18C As shown, it is used for coupling with the sensor. The outer surface of the housing is preferably completely covered by an insulating material (eg, a plastic material) for galvanic isolation, waterproof sealing and mechanical stability.

[0131] The housing 301 is arranged to allow two or more such connectors 300, 300a to be stacked on one another, for example, as shown in FIG. 18, so that the second coil 306 of the connector 300 and the first coil 305a of the second connector 300a stacked on the connector 300 (or vice versa, depending on the order in which the connectors 300, 300a are stacked on one another) together form a first transformer for inductive power transmission therebetween.

[0132] The circular protrusions 314, 314a formed on the top surface of the connector fit into the circular recesses 304, 304a on the bottom of the next connector. Thus, the upper coil 306 of the connector 300, together with the lower coil 305a of the connector 300a, are surrounded by the high magnetic permeability material of the flux concentrators 303, 303a. As a result, the coils are now tightly coupled, which enables efficient power transfer. Arrows 315 show the magnetic flux lines when the coils are actuated as indicated. In this way, stray flux is minimized, avoiding crosstalk from / to the measurement and radio signals. If necessary, conductive sheet material can be added to short-circuit any remaining flux components.

[0133] All components of the connector 300, 300a, including the measuring unit, the battery, the cable connector (PSC unit), are preferably adapted into a circular sealed box 301, 301a representing the housing. Due to the rotationally symmetrical design, no specific positioning of the two connectors in the radial direction is required when stacking, but in this way, the connectors can be easily stacked on top of each other. In addition to the circular shape, other shapes are also possible, for example, with a reduced rotation angle, a square shape, a shape extending in four directions, etc.

[0134] Preferably, the pole tips of the inverted U-shaped core are not covered with (thick) plastic, since this would have a negative effect on efficiency and introduce stray flux. Isolation can be ensured by reducing the plastic thickness to, for example, a few tenths of a millimeter. Alternatively, galvanic isolation can also be ensured, since (composite) ferrite materials may have a high intrinsic resistivity and enable coil and core to be isolated from the inside.

[0135] Preferably, the transmission of magnetic power is not started until a large coupling between the coil and the RF is detected, as described above with respect to FIGS. 10 to 11. Fig.16 In the example shown in FIG. 18 , only the lower coil 305a and the upper coil 306 are used, and the other coils are not actuated at all.

[0136] For reasons of efficient power transfer and high radio SNR, the coupling region should be large enough.Thus, preferably, the coils 305, 306, 305a, 305b and the RF antennas 307, 307a are located on the outer region of the respective connectors 300, 300a.

[0137] The PSC unit 313 for connecting one or more sensors to the connector 300 including the measuring unit 310 is preferably located on the side of the connector 300 in order to have complete stacking freedom. However, the PSC unit 313 can also be located, for example, on the upper part of the connector 300 when being restricted to always having the connector 300 including the measuring unit 310 on the top of the stack.

[0138] Fig.19 Three connectors 300, 300a, 300b are shown stacked on each other, wherein the connectors 300, 300b are identical and configured as shown in Figure 17 and each include a measurement unit 310, 310a, while the connector 300a is configured as shown in Figure 18 and includes a battery 311. The measurement units 310, 310b are therefore fed by the same battery 311 of the connector 300a (therefore, the battery 311 can also be located at different positions, such as at the bottom or top position). In this case, both coils 305a, 306a of the connector 300a are used to supply energy to the measurement units 310, 310b. Many variations of this scheme are possible, for example, receiving power from one connector via one coil while supplying power to another connector via another coil.

[0139] The present invention is applicable to practically including, for example, Figure 2 Any combination of stacked connectors in any type of device used in the system (e.g., patient monitoring system) shown. Therefore, one or more measurement modules, battery units, cable units, and processing units can be easily coupled for cordless transmission of power and / or data. It even enables devices to be linked to each other. Daisy chaining is valuable in body wearable sensing, for example, by connecting a device (e.g., measurement module) to a patient monitor, power supply, or hub via a single connection or cable (including a connector according to the present invention), avoiding cable confusion. This concept is illustrated in Figure 20, which shows the arrangement of several devices in daisy chain form, each device including one or more of the connectors according to the present invention.

[0140] Fig. 20A shows a series coupling and coupled to (e.g. Figure 2 of the type shown) of a central processing unit 20 (e.g., Figure 2 Three measuring modules 30 , 40 , 80 of the type shown are coupled in series. Fig. 20BA cross-sectional view of a stack 320 of three connectors 381, 352, 361 of the type shown in FIG17 is shown, wherein the connector 381 is part of the measuring module 80, the connector 351 is part of the first cable unit 350, and the connector 361 is part of the second cable unit 360. The first cable unit 350 comprises a connector 351, 352 at each end thereof and connects the measuring module 80 with the measuring module 40 having a connector 341 of the same type. The second cable unit 360 comprises a connector 361, 362 at each end thereof and connects the measuring module 80 with the central processing unit 20 having a connector 321 of the same type. The third cable unit 370 comprises a connector 371, 372 at each end thereof and connects the measuring module 40 with the measuring module 30 having a connector 331 of the same type.

[0141] Thus, in this example, the measurement module 80 is connected to two cable units 350, 360. Thus, the cable unit 360 is capable of transmitting power and data for the complex of three measurement modules 30, 40, 80 to and / or from the central processing unit 20. Data and power can be relayed, transmitted and / or exchanged between the stacked connectors. Power transmission can be performed by using additional rectifiers and transmitting electronics (e.g., DC / AC conversion) or by simply sharing the alternating current between the coils, which is the most efficient option in terms of hardware.

[0142] It should be noted that, for example, the connectors 321 and 362 or the connectors 341, 351 and 372 Fig. 20A Other connector stacking arrangements shown are similar to Fig. 20B The arrangement of the stacks 320 shown is similar or identical.

[0143] According to the same principle, Fig. 20C As shown, a star configuration is possible, instead of Fig. 20A Series configuration shown.

[0144] It should be noted that combined power and data transfer via the same cable is preferred, but alternatively any combination of short range radio cable and local battery is also feasible.

[0145] 21-23 illustrate additional embodiments of stackable connectors having alternative connector geometries compared to the connector geometry shown in FIG. 17 . Fig.21A A cross-sectional view of a circular connector 390 is shown, wherein the area outside the flux generator 303 is occupied by the measurement electronics 310 and / or the battery. Fig.21B A top view of the connector 390 is shown. Fig.22A A cross-sectional view of a rectangular connector 391 is shown, and Fig. 22B A top view of the rectangular connector 391 is shown. FIG. 23 is a cross-sectional view ( Fig.23A )、Top view( Fig. 23B ) and simplified cross-section diagram ( Fig.23C ) shows a smart card sized connector 392 which can be clamped between the walls of the patient monitor slot 27. The central processing unit 20 and the connector 392 are coupled via coupling units 321,393.

[0146] In an embodiment, the upper surface and / or the lower surface of the connector according to the invention is completely flat. This makes cleaning easier, for example. Fig.24 25 and corresponding embodiments of connectors 400, 410 are shown. Additional embodiments with other alignment structures or features are possible to ensure precise positioning and close alignment (preferably <1 mm) between flux concentrators of different connectors when stacked together. For example, in certain applications, the gap (with low μ) between flux concentrators (with high μ, including the plastic insulator of the housing) should be <0.5 mm + / - 0.1 mm. The lateral displacement should be small (e.g. <0.5 mm) compared to the geometry of the poles.

[0147] Fig.24 A cross-sectional view of a connector 400 (including a measurement module 310), 400a (including a battery 311) having a housing 407, 407a with a flat main surface 408, 409, 408a, 409a, using a flux concentrator 401, 401a with an H-shaped cross section is shown. Each flux concentrator 401, 401a comprises a first (lower) recess 402, 402a and a second (upper) recess 403, 403a, in which the first (lower) coil 305, 305a is arranged, and in which the second (upper) coil 306, 306a is arranged. The lower coil 305 a of the connector 400 a and the upper coil 306 of the connector 300 together with the lower portion of the flux concentrator 401 a and the upper portion of the flux concentrator 401 form a transformer as indicated by arrow 404 .

[0148] Fig.25A A cross-sectional view of a connector 410 (including a measuring unit 310 ) having a flat surface is shown. Fig.25BA top view of the connector is shown. The connector 410 comprises two flux concentrators 411, 421, each having a U-shaped cross section and forming respective recesses 412 and 422, wherein each recess is formed between two adjacent legs 414, 415 and 424, 425 of a respective U, i.e. between a respective outer ring 414, 424 and a respective inner ring 415, 425 (in this embodiment a central finger). A first coil 417 is arranged in the recess 412 of the first flux concentrator 411, and a second coil 427 is arranged in the recess 422 of the second flux concentrator 421.

[0149] The two flux concentrators 411, 421 can also be regarded as a common H-shaped flux concentrator, wherein the two legs 414, 415, 424, 425 of the H-shaped flux concentrator 421 are arranged adjacent to each other or formed integrally, and wherein the transverse joint between the legs of the H-shape is divided into two joint elements 419, 429, and the two joint elements 419, 429 have a shield 418 arranged between them and perpendicular to the legs 414, 415, 424, 425 of the H-shape.

[0150] The stacking concept can also be converted to a horizontal geometry. This has the benefit of reducing the building height. Fig.26A A cross-sectional view of an embodiment of a connector 430 having a transverse geometry is shown, and Fig.26B 4 shows a top view of the connector 430. The connector 430 includes coils 431, 441 (each having a U-shaped cross section, as shown) arranged in recesses 437, 447 of respective flux concentrators 432, 442 on its left and right sides, respectively. Fig.25A 411, 421 are shown). A ring RF antenna 433, 443 is arranged around the flux concentrators 432, 442. In addition, two power units 434, 444, two RF units 435, 445, two PSC units 436, 446 and a measuring unit 310 are provided. The flux concentrators 432, 442 are therefore arranged to be laterally displaced relative to each other, so that the first flux concentrator 432 and the second flux concentrator 442 are arranged in opposite areas and adjacent to the same surface of the housing. The housing 439 is preferably flat or has a flat surface.

[0151] FIG. 27 shows a daisy chain 440 formed between the measurement modules 30 , 40 by using a cable unit 450 including the connectors 430 c , 430 d shown in FIG. 26 , each of the measurement modules 30 , 40 including the connectors 430 a , 430 b shown in FIG. 26 . Fig.27A shows a cross-sectional view of a daisy chain, Fig.27BA top view is shown.Such a cable unit 450 may comprise two or more such connectors, preferably one at each end, but optionally with additional connectors between the ends.

[0152] FIG. 28 is a cross-sectional view ( Fig.28A ) and top view ( Fig.28B ) schematically shows a body-worn sensor arrangement 460. The body-worn sensor arrangement 460 comprises a stackable support layer 461 carrying a cable unit 451, which is similar or identical to the cable unit 450 shown in FIG. 27, and comprises connectors 452, 453, which are like connectors 430c, 430d or have only connectors like Fig.28A A single coupling unit is shown. One or more measuring modules 30 and / or battery modules 90 (including batteries) may be arranged on the cable unit, each measuring module including a connector 430a, 430b.

[0153] The measuring modules 30, 40, 80, the battery module 90 and the cable unit 450 can also be used with Fig.29 The same lateral geometry concept schematically shown in FIG is connected to, for example, a patient monitor or a central processing unit 20. In addition, any combination of vertical stacking and lateral connection can generally be used with the connector as proposed by the present invention. For example, a measurement module can have both vertically stacked devices and horizontally stacked devices.

[0154] A battery module including the connector according to the present invention will be described in more detail below.

[0155] As described above, the plug-in measurement module is coupled to the central processing unit via the proposed connector using magnetic power supply and RF data communication. In addition, via its RF channel, the battery (or any other energy storage element) can form part of a network (e.g. a patient network) and can be coupled to other devices (e.g. measurement modules and central processing unit) in the same way. This Fig.30 The schematic diagram shows that Fig.30 A schematic diagram of another embodiment of a system 13 according to the present invention comprising a measurement module 30 , a central processing unit 20 and a battery module 90 is shown.

[0156] In the wireless measurement scenario, the bidirectional battery module 90 can be snapped onto the measurement module 30 to supply energy magnetically via the proposed connector. Optionally, the measurement module 30 itself can include a small buffer battery 37 (or any other energy storage element) for temporarily bridging the transition time between the wired scenario and the wireless scenario.

[0157] The battery module 90 preferably includes a battery 91 (also referred to as a battery cell) and a coupling unit 92, the coupling unit 92 being used for magnetic power transmission between the battery module and other devices, for example, loading the battery when the battery module 90 is coupled to the central processing unit 20, and loading the battery 37 of the measurement module 30 when the battery module is coupled to the measurement module 30. Optionally, a device for data transmission may also be provided in the battery module 90.

[0158] exist Fig.35 A more detailed schematic diagram of a battery module 90' ​​is shown in Figure 1, wherein the battery module 90' ​​is used to wirelessly exchange data and power between the battery module and another device of a system, in particular a patient monitoring system, to which the battery module 90' ​​is coupled. The battery module 90' ​​is configured for mobile use and coupling with different devices of the system, such as Fig.30 As shown in the figure. The battery module 90' ​​includes a sealed housing 93, a battery cell 91 for storing electric energy, a data storage unit 94 for storing data, and a connector 95. The connector includes a data transmission unit 96 and a magnetic coupling unit 92, the data transmission unit 96 is used to send data to another device of the system having a mating connector and / or receive data from another device of the system having a mating connector, and the magnetic coupling unit 92 is used to send power to another device of the system having a mating connector and / or receive power from another device of the system having a mating connector by using inductive coupling.

[0159] The sealed housing preferably provides a completely isolated enclosure to ensure galvanic isolation of, for example, 5 kV between measurements, i.e., there are almost no gap losses with respect to inductive coupling. The gap between the coil of the magnetic coupling unit of the battery module 90' ​​and the other device to which the battery module is coupled is well defined, so that there is no need for adaptive and complex tuning out of stray inductances. Therefore, a coupling factor k of k>0.95 can be achieved due to the small and well-defined magnetic gap and low stray fields. This provides high power efficiency, which is advantageous for, for example, daisy chains.

[0160] Optionally, a second connector 97 is provided for simultaneously sending data to and / or receiving data from two other devices of the system and / or for simultaneously sending power to and / or receiving power from two other devices of the system.

[0161] The connector and its elements may be configured as explained above with respect to other devices and other embodiments. This applies in particular to the magnetic coupling unit 92 and the data transmission unit 96, which may be configured as disclosed herein, for example, as shown in FIGS. Fig.15 Or as shown in any one of Figures 17 to 28.

[0162] The battery 91 can be, for example, a rechargeable battery, a disposable battery or a supercapacitor, and can be adapted into a smooth sealed plastic box to well prevent mechanical damage and liquid. It can be physically attached to (i.e., in close contact with) another device (e.g., a measurement module, a cable unit or a patient monitor) having the proposed connector, for example, via an easy-to-use snap or slide-in mechanism. A permanent magnet or alignment structure can be used to align and fix its position to obtain optimal power and radio transmission. When the battery 91 is empty, the battery module 90 can be attached to any device in a system with a compatible connector (optionally via a cable), and can charge, for example, a patient monitor, a hub or a dedicated battery charger. Preferably, all elements are coupled to each other using the same inductor / data connector topology throughout the architecture. This enables charging the battery anywhere, providing a huge improvement in battery management.

[0163] Rechargeable battery life is almost always defined by manufacturers and testers as the number of complete charge-discharge cycles. In addition to cycling, the degradation rate of lithium-ion batteries is strongly dependent on temperature; if stored or used at higher temperatures, for example, when applied to the human body, lithium-ion batteries degrade much faster.

[0164] Therefore, by using voltage and / or current sensor(s) (usually Fig.35 The health and charge status of the battery can be continuously determined based on temperature sensors, absolute time, and charge and discharge curves (represented by sensor unit 98 in FIG). Based on this information and historical data, self-diagnosis can be performed and communicated in the patient network to indicate the need for recharging, replacement, or any fault conditions. Historical data can be stored locally (e.g., in the battery module) and shared in the network. Many scenarios are possible for this.

[0165] The battery module 90' ​​may also include a processing unit 99 for data processing, time counting, self-diagnosis and safety of received data. When applied to the measurement module 30, the processing unit may also be configured to calculate the expected operating time.

[0166] In addition, Fig.16As illustrated, the battery module 90' ​​may include a detection unit 273 and a control unit 274, wherein the detection unit 273 is used to detect the strength of the magnetic coupling between the magnetic coupling unit and the magnetic coupling unit of another device, and the control unit 274 is used to switch the data sending unit to a low power mode and / or enable the magnetic coupling unit when the detected magnetic coupling is higher than a first threshold and / or the detected increase in the magnetic coupling is higher than a second threshold, and to switch the data sending unit to a high power mode and / or disable the magnetic coupling unit when the detected magnetic coupling is lower than a third threshold and / or the detected decrease in the magnetic coupling is higher than a fourth threshold.

[0167] The main standards for wireless power transmission are the Qi standard and the Power Matters Technology (PowerMat) standard. Their main application is in the field of wireless charging. Qi also includes basic positioning and identification mechanisms for devices, low-power standby modes, and power control.

[0168] An additional on-off switch using reed contacts and permanent magnets (e.g. as part of a click-fastening mechanism) can be used as an additional layer of safety and battery leakage prevention, but there may also be other means of stacking detection (e.g. optical, capacitive, or ultrasonic).

[0169] Lithium-ion and lithium-polymer batteries are favored for their high energy density per unit mass and large-scale use in the consumer sector. They have appropriate electronics to observe their charge status and prevent overheating. Moreover, the Qi standard already has some appropriate basic devices to identify the payload. These can be used according to the present invention. These basic protection and monitoring devices can be integrated into a complete architecture according to the present invention by combining magnetic coupling with RF coupling as communication devices, local intelligent safety monitoring and by connecting to the patient network. For example, the lack of a valid identifier and / or the presence of a local fault condition can be a reason to abandon or not start magnetic power transmission.

[0170] The state of charge can be used to determine how long the battery can be used for a particular measurement. This can be shown, for example, on a patient monitoring display. Optionally, when attached to a measurement module, a visual indicator or an audible indicator on the battery itself can indicate, for example, when the available measurement time is less than 1 hour before replacement or charging should occur.

[0171] As described above, integrating batteries in a medical environment has a significant impact on safety, usage, and workflow. Constraints include absolute safety, possible shape, small weight and volume, easy replacement / pluggability by nurses, easy cleaning, large capacity, and charge rate during wear. The battery module can be a closed box with a completely wireless connection for both charging and providing energy. The proposed architecture provides an easy-to-clean mechanical connection. In addition, they can be replaced in seconds while the measuring device remains in place.

[0172] A cable unit including a connector according to the present invention for connecting other devices of a network / system will be described in more detail below.

[0173] exist Fig.31 , the overall layout of the cable unit 500 is shown in FIG. The cable unit 500 includes a cable 510 and connectors 520, 530 at each end of the cable 510. Each connector 520, 530 includes a magnetic coupling unit 521, 531 and a data transmission unit 522, 532. The cable 510 includes a first wire pair 511 (e.g., twisted wire) connecting the magnetic coupling units 521, 531 and a second wire pair 512 (e.g., twisted wire) connecting the data transmission units 522, 532.

[0174] Fig.32 The use of a cable unit 500 in a high acuity environment is illustrated, in this example for connecting a measurement module 30 and a central processing unit 20. Such a cable unit 500 can be used in an OR (operating room) or ICU (intensive care unit) environment to ensure data integrity and power consistency for measurements. The two wire pairs 511, 512 are preferably thin and flexible as used in catheter technology. Additional conductive shielding or ferrite common mode coils can be added for additional robustness and performance. This approach ensures a sufficiently high signal-to-noise ratio for radio signals due to its low RF attenuation and shielding properties. Due to the frequency used for contactless powering The ratio to the radio (2.4GHz) is large, so the internal crosstalk is controllable.

[0175] To implement the main function of this cable unit 500 to form a protected conduit for radio and power signals, many options are possible.

[0176] One option is a completely passive cable unit consisting of two wire pairs (such as Fig.31 , Fig.32). Basically, RF data and power can be transmitted in both directions on the cable unit. Twisted wires for power and coaxial or balanced transmission lines for RF data can be used. Additionally, passive components can be added to the connector to further improve the RF transmission, for example by filtering and impedance matching, to improve the (power) transmission by, for example, flux concentrators or passive identification (optical tags).

[0177] Optionally, power and radio signals can be combined in one single wire pair (or coaxial cable). Attaching only one connector of a completely passive cable to, for example, a measurement module will neither increase magnetic coupling nor RF coupling. Both connections are achieved until pairing is initiated.

[0178] Another option is an active cable. There are active components (in one or both connectors) to convert the magnetic power signal into a purified / stabilized direct current or sinusoidal alternating current before sending it through the cable. This limits crosstalk and interference caused by the power signal entering the radio channel. The most logical location for the components is in the connector(s), but they can also be distributed on (parts of) the cable unit, for example on a flexible foil integrated in the cable bushing.

[0179] The data radio signal can be amplified, remodulated (transponder), buffered or (actively) impedance transformed to match the RF cable properties. Alternatively, conversion to another frequency band or baseband can enhance the integrity of the signal even more, for example by converting to the format of a serial bus such as USB, RS232 or TCP / IP. Part of the power is used to power the active components.

[0180] Each connector can be arranged as a node and act as a node itself and is part of the patient network, including a unique identifier, radio and network stack for pairing, and magnetic powering. Additional radios can be added to relay radio signals (e.g., in a daisy chain) or implement separate channels for patient network management. Active cables may only transmit data or power in one direction; therefore, more pairs may be required per cable, or more cables may be required for bidirectional transmission.

[0181] According to another option, conversion of RF signals to the optical domain may be provided, which provides the ultimate level of data integrity and potentially also allows for thinner cables.

[0182] Obviously, the cable unit may include only a power channel or only a data channel.

[0183] Identification tags (RFID) or radio units may be added to cable units or connectors for identification and data management.

[0184] Preferably, from the user's perspective, the cable unit should be able to transmit RF data and power in both directions. This may require the use of more wire pairs, for example in the case of active components being applied.

[0185] Fig.33 The use of the cable unit 500 in a lower acuity environment is illustrated, in which case the measurement module 30 (or battery module 90) and central processing unit 20 are connected only when needed to improve RF performance (e.g. in a crowded area) or for power or charging reasons (i.e. to save battery capacity for mobile use). The measurement modules can be connected together in a chain to avoid cable clutter.

[0186] exist Fig.36 A more detailed schematic diagram of a cable unit 500' for connecting devices in a system to enable wireless exchange of data and / or power between the devices is schematically shown in Figure 1. As explained above, the cable unit 500' comprises a cable 510 and connectors 520, 530 arranged at each end of the cable. Each of the connectors comprises a data transmission unit 522, 532 for transmitting data to and / or receiving data from a device having a mating connector, and a magnetic coupling unit 521, 531 for transmitting power to and / or receiving power from another device of the system having a mating connector by using inductive coupling.

[0187] The cable unit 500' further comprises a (sealed) housing 523, 533 arranged at each end of the cable 510, wherein one or more connectors 520, 530 arranged at the respective ends of the cable are arranged in the housing 523, 533. The sealed housing is preferably configured as disclosed herein in the context of other devices to allow the cable unit 500' to be stacked to other devices having mating connectors.

[0188] The connector and its elements may be configured as explained above with respect to other devices and other embodiments. This applies in particular to the magnetic coupling units 521, 531 and the data transmission units 522, 532, which may be configured as disclosed herein, for example, as shown in FIGS. Fig.15 Or as shown in any one of Figures 17 to 28.

[0189] The cable unit 500 ′ may further include an electronic circuit 501 , and the electronic circuit 501 is used to process, convert and / or store received data.

[0190] In addition, if Fig.16As illustrated, the cable unit 500', in particular, each connector 520, 530 may include a detection unit 524, 534 and a control unit 525, 535, wherein the detection unit 524, 534 is used to detect the strength of the magnetic coupling between the magnetic coupling unit (of the respective connector) and the magnetic coupling unit of another device, and the control unit 525, 535 is used to switch the data sending unit (of the respective connector) into a low power mode and / or enable the magnetic coupling unit (of the respective connector) when the detected magnetic coupling is higher than a first threshold and / or the detected increase in magnetic coupling is higher than a second threshold, and to switch the data sending unit (of the respective connector) into a high power mode and / or disable the magnetic coupling unit (of the respective connector) when the detected magnetic coupling is lower than a third threshold and / or the detected decrease in magnetic coupling is higher than a fourth threshold.

[0191] As an alternative, the cable unit 500', in particular each connector 520, 530 may include a proximity detector 526, 536 for detecting the proximity of the cable unit of another device (i.e., for detecting whether there is only a small air gap between them), and a control unit 527, 537 for switching the respective data transmission unit 522, 532 (of the respective connector) into a low power mode and / or enabling the magnetic coupling unit (of the respective connector) when a device is detected to be close to the cable unit, and switching the data transmission unit (of the respective connector) into a high power mode and / or disabling the magnetic coupling unit (of the respective connector) when no device is detected to be close to the cable unit. Such a proximity detector and control unit may also be used in other embodiments of the connector and in other devices disclosed herein.

[0192] Various proximity detection methods can be used, such as the received signal strength indication (RSSI) method, for example, standard Bluetooth, Bluetooth Low Energy (BTLE), and Wi-Fi. Other examples of proximity detection methods include differential methods such as ultra-wideband (UWB), optical methods using, for example, infrared (IR) wavelength ultrasound, and NFC. Proximity detection methods such as IRDA, UWB, and NFC typically use both standard data transfer mechanisms and proprietary data transfer mechanisms. In an example, proximity detection occurs when two devices are, for example, within 0.5 mm + / - 0.1 mm of each other, whereby other distances can be used.

[0193] In general, direct or indirect means can be used to detect the proximity of a device to another device. The actual distance between two devices that can be detected as "close" depends on, for example, the magnetic design; one criterion may be that the magnetic coupling is greater than 90%, or preferably greater than 95%, or ultimately greater than 99%. In an exemplary design, a magnetic coupling is used. With a magnetic distance of 2*0.25 mm (due to the plastic housing of 2*0.25 mm), this may be understood as "very close". However, other distances may be used instead, depending on the specific design and / or application.

[0194] Finally, within each housing 523, 533, a second connector 540, 550 may be arranged for simultaneously sending data to and / or receiving data from two devices, and / or for simultaneously sending power to and / or receiving power from two devices. The second connector 540, 550 is typically configured in the same manner as the first connector 520, 530.

[0195] The proposed cable unit can be used to connect the measuring module with the monitoring device. Fig. 20A and Fig. 20C Daisy chain as shown as well as star configurations are possible. Cable units may be coupled laterally or vertically on top of each other or with a third component in between. Alternatively, the distribution cable unit may have multiple branches to physically connect the components.

[0196] The pairing of devices proposed by the present invention will be explained below.

[0197] A first option for pairing is to perform the pairing manually, for example during attachment of the measurement module to the person's body. By bringing the device physically close to the other device, identifiers are exchanged, which in practice means that the device is added to the network of devices, for example to the patient's network. This is easy to achieve during the first attachment of the measurement module and for mobile patients.

[0198] The order of connection is generally not important; each network member is able to communicate and update the network status via the master device in a specific standard (such as Bluetooth LE). Visual or audible information on the device can indicate its connection status. It can, for example, indicate which devices are paired to the patient network, and can indicate a loss of RF connection to the hospital network or to a patient monitor of, for example, a mobile patient. In this case, the patient network needs to reconnect (automatically or manually) to another radio link.

[0199] The start mechanism is activated when two conditions are met:

[0200] 1. The level of magnetic coupling increases, which can be detected from the induced voltage in the secondary coil and the current in the primary coil or the resonant frequency of the component. When this condition is met, the RF radios (can be via the master device) begin to communicate with each other.

[0201] 2. When the strength of the received RF signal is also above a predetermined level, correlation is started. Alternatively, the deviation from the transmitter antenna impedance (voltage standing wave ratio VSWR, reflected wave) can be included as an additional check, indicating RF absorption of the transmitted signal.

[0202] This mechanism is repeated to switch the membership of the patient network, i.e., the master device is aware of all devices in a particular patient's network; it switches between joining and leaving. Network membership may be displayed by visual actuators, tactile actuators, or auditory actuators (e.g., LEDs, displays, buzzers, pagers, vibrators, etc.). Additionally, a mechanical switch or keypad code may be used to force leaving the network.

[0203] The patient may have a patch that includes patient network functionality as an additional identification and location means to enforce that the measurement (or sensor) is attached to the correct location on the correct patient.

[0204] The second option for pairing is to use Fig.31 The cable unit 500 shown connects a stationary (eg, OR or ICU) patient to a patient network. By connecting the cable unit between the measurement module and the monitoring device for a short period of time, the magnetic coupling and RF amplitude will increase above a certain level, which will trigger the pairing mechanism.

[0205] A third option for pairing is to use a contactless storage module, which can be used as an intermediate storage container to transfer identifiers between components in the patient network. Fig.34 The figure shows that Fig.34 A schematic diagram of a fifth embodiment of a system 14 according to the invention comprising a storage module 95 is shown. By bringing the contactless storage module 95 into close proximity with another component 20 or 30 having a mating connector, the identifiers are interchanged and used to update the patient network. An additional mechanical button or proximity detector may be used to trigger the exchange. Preferably, only one identifier can be stored and transmitted to avoid ambiguity.

[0206] The contactless storage module 95 can have the physical size and shape of a pencil, smart card or small box like the measuring module. Like other devices including the connector according to the present invention, in addition to the storage element 98, it also includes a magnetic coupling unit 96 and a data transmission unit 97 (e.g., radio hardware) to couple to other devices with a mating connector.

[0207] A fourth option for pairing is to use additional triggering means. A button or proximity detector (e.g., using optical, magnetic, ultrasonic technology) can be added as a condition to initiate the pairing process. Additional triggering means are beneficial as an additional layer of robustness to omit components for detecting the level of coupling (e.g., no RF or magnetic coupling measurement is required). Additionally, in the case of a pencil-type device, the RF antenna and coil can be located in the tip; the maximum coupling can be below a predetermined threshold for triggering the association process.

[0208] exist Fig.37 A more detailed schematic diagram of a device 600 for wirelessly transmitting data and / or power between a device of a system and another device, the system being in particular a patient monitoring system, is shown in FIG. The device 600 is configured to apply the above-described method for pairing and comprises an identification unit 601 for storing a unique identifier of the device and a connector 602. The connector 602 comprises a data transmission unit 603, which is arranged to transmit data to another device of the system having a mating connector and / or receive data from another device of the system having a mating connector, a magnetic coupling unit 604, and a detection unit 605, wherein the data transmission unit 603 is arranged to transmit data to another device of the system having a mating connector and / or receive data from another device of the system having a mating connector, the magnetic coupling unit 604 is used to transmit power to another device of the system having a mating connector and / or receive power from another device of the system having a mating connector by using inductive coupling, and the detection unit 605 is used to detect the strength of the magnetic coupling between the magnetic coupling unit and the magnetic coupling unit of the mating connector of the other device, and to detect the strength of the data received by the data transmission unit from the data transmission unit of the other device.

[0209] The device 600 also includes a control unit 606, which is used to control the data sending unit 603 to send the unique identifier of the device to another device and / or receive the unique identifier of another device when a) the detected strength of the received data is higher than the data strength threshold and / or the detected increase in the strength of the received data is higher than the data strength increase threshold and b) the detected magnetic coupling is higher than the magnetic coupling threshold and / or the detected increase in the magnetic coupling is higher than the magnetic coupling increase threshold.

[0210] The device 600 may further include a storage unit 607 for storing unique identifiers of other devices received by the data transmitting unit.

[0211] The control unit 606 can be configured to control the data sending unit to additionally send the unique identifier of other devices stored in the storage unit and / or receive the unique identifier of other devices when a) the detected intensity of the received data is higher than the data intensity threshold and / or the detected increase in the intensity of the received data is higher than the data intensity increase threshold and b) the detected magnetic coupling is higher than the magnetic coupling threshold and / or the detected increase in the magnetic coupling is higher than the magnetic coupling increase threshold.

[0212] The detection unit 605 may be configured to detect impedance, resonant frequency and / or induced voltage for detecting the strength of magnetic coupling, and / or detect the signal strength and / or antenna impedance of the antenna of the data transmitting unit for detecting the strength of received data. The strength of magnetic coupling is generally referred to as a magnetic coupling factor k (0 <= k <= 1).

[0213] In case the components are already connected, this is clear from the availability of power and a strong RF signal. The attachment of a new component can be detected by using a polling mechanism to check for an increase in magnetic coupling (and optionally an RF signal for data transmission). The detection of disconnected components can be performed by the reverse process: the polling mechanism measures the decrease in the strength of the magnetic coupling by using, for example, impedance, resonant frequency and / or induced voltage (and optionally an RF signal). Optionally, the RF signal strength can be additionally measured.

[0214] Typically, a first transmission of the unique identifier is interpreted as a request to couple the device to the system, and a second transmission of the unique identifier is interpreted as a request to decouple the device from the system.

[0215] The device may further comprise an indicator 608, in particular a visual indicator, a tactile indicator or an audible indicator, for indicating a coupling state of the device with the system.

[0216] Still further, the device may include a user interface 609 for enabling a user to initiate the sending of a unique identifier or the coupling or decoupling of a request message.

[0217] Still further, the device may include a proximity detector 610 for detecting proximity of the device to other devices, wherein if it is additionally detected that the device is close to other devices, the control unit controls the data transmission unit to send the unique identifier of the device to the other device and / or receive the unique identifier of the other device. The proximity detector may be configured as explained above with respect to other embodiments.

[0218] The connector 602 and its elements may be configured as explained above with respect to other devices and other embodiments. This applies in particular to the magnetic coupling unit 604 and the data transmission unit 603, which may be configured as disclosed herein, as shown in FIGS. 10 to 11 . Fig.15 Or as shown in any one of Figures 17 to 28.

[0219] Finally, the device 600 may also include a data unit 611 for generating and / or receiving data, and / or a power unit 612 for supplying and / or consuming power.

[0220] One major advantage of the present invention is that it provides a universal approach that can generally serve all patient monitoring applications, which is a key factor in achieving cost reduction. Additional advantages are modularity and direct compliance with existing wireless measurement connection standards.

[0221] The application of the present invention is not limited to patient monitoring, but can be extended to isolated modules (sensors, actuators) connected to a common entity, for example in automobile production or livestock breeding (central milking machine connected to multiple cows). In addition, the present invention is not limited to the types, forms and numbers of antennas or coils explicitly disclosed, which are only to be understood as examples. The components used in the disclosed embodiments can also be configured to comply with the Qi standard or other wireless power standards, and if possible from a technical point of view, according to the present invention, standard components complying with the Qi standard can also be used for individual components. In addition, the device can include devices for vertical stacking and horizontal stacking, and include corresponding coupling devices for coupling in the respective directions, that is, the device can include, for example, Fig.25A and Fig.26A The connector combination shown.

[0222] Although the present invention has been illustrated and described in detail in the drawings and the foregoing description, such illustration and description should be considered illustrative or exemplary rather than restrictive; the present invention is not limited to the disclosed embodiments. Other variations of the disclosed embodiments can be understood and implemented by those skilled in the art in practicing the claimed invention by studying the drawings, the disclosure, and the claims.

[0223] In the claims, the word "comprising" does not exclude other elements or steps, and the word "a" or "an" does not exclude a plurality. A single element or other unit may fulfill the functions of several items recited in the claims. Although certain measures are recited in mutually different dependent claims, this does not indicate that a combination of these measures cannot be used to advantage.

[0224] Any reference signs in the claims should not be construed as limiting the scope.

Claims

1. A battery module for wirelessly exchanging data and power between the battery module and another device of a plurality of devices in a system, the battery module being coupled to the other device, the other device being a measurement module or a central processing unit, the battery module comprising: - Sealed housing, - a battery cell (91) for storing electrical energy, - a data storage unit (94) for storing data, and - a connector, comprising a data transmission unit (96) and a magnetic coupling unit (92), the data transmission unit being used to transmit data to the other device of the system having a mating connector and / or to receive data from the other device of the system having a mating connector, the magnetic coupling unit being separate from the transmission unit (96) and being used to transmit power to the other device of the system having a mating connector and / or to receive power from the other device of the system having a mating connector by using inductive coupling, wherein the battery module is configured for mobile use and coupled to the plurality of devices of the system, and The sealed housing is configured to allow the battery module to be stacked to the plurality of devices having mating connectors, and to allow the plurality of devices including the battery module to be stacked on top of each other.

2. The battery module according to claim 1, Also includes: A second connector (97) is used to simultaneously send data to and / or receive data from two other devices of the system, and / or to simultaneously send power to and / or receive power from two other devices of the system.

3. The battery module according to claim 1, in, The battery unit (91) includes a rechargeable battery or a capacitor.

4. The battery module according to claim 1, Also includes: A sensor unit (98) includes a temperature sensor, a voltage sensor and / or a current sensor.

5. The battery module according to claim 1, Also includes: The processing unit (99) is used for performing data processing, time counting, self-diagnosis and safety on the received data.

6. The battery module according to claim 5, in, The processing unit (99) is configured to calculate an expected operating time when applied to a measurement module.

7. The battery module according to claim 1, further comprising: - a detection unit (273) for detecting the strength of magnetic coupling between the magnetic coupling unit and a magnetic coupling unit of another device, and - A control unit (274) for switching the data transmission unit into a low power mode and / or enabling the magnetic coupling unit if the detected magnetic coupling is above a first threshold and / or the detected increase in magnetic coupling is above a second threshold, and for switching the data transmission unit into a high power mode and / or disabling the magnetic coupling unit if the detected magnetic coupling is below a third threshold and / or the detected decrease in magnetic coupling is above a fourth threshold.

8. The battery module according to claim 1, in, The data transmission unit (96) is configured to transmit data by using RF transmission, optical transmission, capacitive coupling or near field communication.

9. The battery module according to claim 1, in, The connector further comprises a carrier (202), The data transmission unit (96) comprises an RF antenna (204) and an RF circuit (208), wherein the RF antenna is arranged in or on the carrier, and the RF circuit is used to drive the RF antenna and / or obtain an RF signal received by the RF antenna.

10. The battery module according to claim 1, in, The magnetic coupling unit (92) includes a flux concentrator and one or more coils, the flux concentrator is used to concentrate magnetic flux, and the one or more coils are arranged around a portion of the flux concentrator.

11. The battery module according to claim 1, in, The magnetic coupling unit (92) comprises: - a flux concentrator having at least partially a U-shaped cross section, a recess (304) being formed between the legs of said U, - a first coil arranged in a recess (304) of the flux concentrator, and - a second coil (306) arranged outside the recess (304) in which the first coil is arranged, The sealed housing is arranged to allow the battery module to be stacked onto other equipment having a mating connector, so that the first coil of the connector together with the second coil of the connector stacked onto the connector forms a first transformer for inductive power transmission between the two, and / or the second coil (306) of the connector together with the first coil of the third connector (300a) stacked onto the connector forms a second transformer for inductive power transmission between the two.

12. The battery module according to claim 1, in, The system is a patient monitoring system.

13. The battery module according to claim 3, in, The capacitor is a supercapacitor.

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