Method and device for recording biosignals

Abstract

Device for recording biosignals comprising: a Pneumo-T adapter designed to combine the device with common CPAP, BiLevel and APAP titration home ventilation therapy systems, at least one sensor a mobile control unit connected to the sensor, wherein the mobile control unit is designed as a handheld device attachable to the patient, comprising: a storage unit for data storage, wherein the storage unit is designed as a memory card, at least one interface for data transmission, wherein the interface is designed for connection to peripheral, therapy or diagnostic devices, at least one free connection slot in the area of ​​the handset to add at least one additional sensor, a sensor test device and a signaling means for signaling an output of the sensor test device, a gain adjustment designed to keep the amplitude of the signals from at least one sensor within a predefined range.

Description

[0001] The device according to the invention relates to a data recording system for acquiring, recording, and storing biosignals, for example, during sleep. It serves to detect sleep-related breathing disorders and accompanying risk factors, as well as other sleep disorders (e.g., restless legs syndrome), to support diagnosis, therapy initiation, and therapy monitoring. Areas of application include inpatient and outpatient examinations in sleep laboratories, as well as outpatient examinations in the non-clinical, sleep medicine field. The method relates to the control of such a data recording system.

[0002] US Patent 6,454,708 B1 describes a sensor band with two sensors and a memory card. The sensor band is intended for use in the vicinity of a patient.

[0003] From DE 43 29 898 A1, various self-contained electrodes are known that communicate with an evaluation station.

[0004] The methods and devices known to date are not yet sufficiently suitable to meet all the requirements for the optimal operation of a mobile data recording system.

[0005] The object of the present invention is therefore to improve a device of the type mentioned in the introduction.

[0006] This problem is solved according to the invention by the features of the main claim.

[0007] A further object of the present invention is to provide an improved method of the type mentioned in the introduction.

[0008] This problem is solved according to the invention by the features of the subsidiary claim.

[0009] The use of a memory card, for example, decouples data acquisition and data processing. This allows for a compact and lightweight mobile device that initially stores the acquired data. After data acquisition is complete, or in parallel but independently of the data acquisition process, the data can be further processed or prepared at a separate location.

[0010] The drawings schematically illustrate exemplary embodiments of the invention. They show: Fig. 1. Multiple views of a handset, Fig. 2. Several illustrations of the sensors used, Fig. 3. Several illustrations to demonstrate functional components of a processing unit, Fig. 4 illustrations of belts for mobile applications, Fig. 5 two application examples, Fig. 6 another application example, Fig. 7. A further modified application example, Fig. 8 a representation of the overall system and Fig. 9 an example measurement curve.

[0011] Fig. Figure 1 shows a handset with a pressure port (1) for connection to a pressure measuring hose, electrode ports (2), a RIB (3), and a port (4) for an abdominal sensor (35) not shown. Also visible are LEDs (5), a button (6), and a battery lock (7), which will be explained in more detail below. Furthermore, a port (8) for a charging / data transfer cable and a battery (9) are visible. Preferably, a second pressure port (10) is provided. The functionality is further enhanced by a thorax sensor (11) and a port (12) for a pulse oximetry sensor.

[0012] An insert card (13) with application locations is provided on the back of the handset. A Z-electrode (14) and a connector (15) are also visible. The connector (15) is used to connect to a device in Fig. 2. The airflow snoring sensor (16) or the airflow oral sensor (27) shown. The connection (1) is for connection to an airflow snoring nasal cannula (22) or a pressure measuring tube (28). The connections (1, 10) together serve for connection to a Pneumo-T adapter (33).

[0013] Fig. Figure 2 shows, in addition to the sensors already mentioned above for connection to the handset, sensor beads (17), a sleeve (18), a microphone (19), a mounting plate (20) and a sensor connector (21). Also shown are a sleeve (23), cannulas (24), a tab (25) and a connection (26) of the airflow anti-snoring nasal cannula (22).

[0014] The pressure measuring hose (28) includes a connector (29), a connecting hose (30), a plastic hose (32), and a threaded fitting (31) for a CPAP connection. A pulse oximetry sensor (34) and an abdominal sensor (35) are also shown.

[0015] The handset is typically connected to an evaluation unit, which may be a personal computer. The evaluation unit includes a CD-ROM drive (36), a charger (37) with power supply (38) and plug (39), a charging / data transfer cable (40), and a USB cable (41). A converter box (42) is equipped with a socket (43) for the charging / data transfer cable (40), a USB socket (44), and a charger socket (45). Data transfer from the handset to the evaluation unit can also be performed directly by inserting a memory card (46).

[0016] Fig.Figure 4 shows a device belt (47) and an abdominal belt (48) to support a mobile application.

[0017] The measured data is stored in the device on a CompactFlash® card and transmitted online to the PC via cable or optionally wirelessly. For mobile use, the data stored in the device can either be transferred to the PC via a USB interface or read into the software using a card reader on the CompactFlash® card.

[0018] The device according to the invention consists, for example, of the following components: A) Handset consisting of: -Basic unit -Sensors -Application parts -Li-ion battery - Medically approved power supply unit (secondary side) with combination cable for charging the battery and for transferring stored data via a galvanically isolated USB interface (converter box) to a PC -According to the invention, a mobile control unit is a component of a handset and / or a base unit. B) PC software: The software can be run under the operating systems Windows 2000 from SP 2 onwards, Windows XP Professional and Home Edition. C) Non-medical electrical devices: -Power supply unit (primary side) -USB / TCP / IP converter -Bluetooth® USB adapter CompactFlash® Card Reader -PC system (third-party accessories).

[0019] The components have the following intended use, or rather, they record the following sleep-related parameters: Basic unit • at least 4 freely configurable electrophysiological channels (E..G1 / E..G4) that can be optionally set for the parameters EMG, EOG, EEG and ECG with corresponding sensors; • Thoracic and abdominal movements; • Oxygen saturation (SpO2; pulse oximetric); • Pulse rate (pulse oximetry); • Nasal breathing flow; • Oral and nasal airflow; • Mouth breathing; • Snoring; • Patient position; • xPAP printing; • Heart rate; • Pulse wave (pulse oximetry; • Oxygen saturation quality index (pulse oximetry) • cHB, SaCo, Sa Met. Sensors • Sensors for the electrophysiological channels; • Effort sensors (thoracic and abdominal movements); • Pulse oximetry sensor for measuring oxygen saturation, pulse rate and pulse wave; • Airflow snoring sensor (thermistors and microphone); • Airflow-anti-snoring nasal cannula (pressure sensor); • Oral thermistor for detecting mouth breathing during therapy monitoring; • Pneumo-T adapter for recording respiratory flow, snoring and xPAP pressure (pressure sensor). Converter box and power supply

[0020] The converter box serves for wired data transmission of the data stored in the device. Data transmission is galvanically isolated via a USB interface. Simultaneously, the device according to the invention is charged via the power supply unit, or continuously powered. PC software

[0021] The PC software is used for the acquisition, storage, processing, visualization, evaluation, documentation, and archiving of patient-related biosignals. This serves to support the diagnosis, treatment initiation, and monitoring of sleep disorders. Device software

[0022] The device software is used to record, store, process, and analyze biosignals. This supports the diagnosis, treatment adjustment, and monitoring of sleep disorders. The device software communicates with the PC software via a secure data transmission protocol. Non-medical electrical devices • Reader for reading the data stored on the CompactFlash® card; • Online module for wireless data transmission (Bluetooth USB adapter); • USB to TCP / IP converter; • PC system (third-party accessories). • The device according to the invention generates information signals (e.g., battery charge level) that are graphically visualized and stored by the PC system. These information signals serve to verify the presence of the signals to be recorded, as well as to check the functionality of the device. This prevents erroneous recordings and eliminates the need for repeating the night measurement. • The system does not generate alarms. • The automatic analyses (PLM, snoring, sleep stage, arousal and cardiorespiratory analysis) are performed offline from the signals stored in the PC and support the evaluator in the diagnosis of sleep disorders, as well as initiating and monitoring therapy. • The PC software is used for visualizing, evaluating, documenting, and archiving patient-specific long-term studies for diagnosing sleep disorders. The system is configured for this purpose, and the transferred data is automatically analyzed offline. The software allows users to enter comments. Manual reclassification of the analysis results by the evaluator is also possible. • After instruction by specialist personnel and using the patient's instructions for use, the patient is able to apply the sensors and the device himself.

[0023] The device according to the invention processes and stores all measured signals on the integrated CompactFlash® card. The data is read out either via a USB cable or by reading the CompactFlash® card with a reader. In stationary operation, the device according to the invention can transmit the acquired data online, either wirelessly or via cable, to the software, where the data is additionally stored.

[0024] The online monitoring with the device according to the invention allows the use of existing networks in clinics. If data is lost, for example, when leaving the examination room, it can be supplemented with data stored on the CompactFlash® card. The device according to the invention is powered by a replaceable battery pack, making it independent of the mains power supply. No stored measurements are lost when the battery is replaced. The device can also be permanently powered and operated via the data transmission cable.

[0025] The device according to the invention has a built-in position sensor. The sensor registers whether and when the patient is lying on their stomach, back, or side. The device also has an effort sensor integrated into the housing. This integration reduces cleaning effort and increases the sensor's lifespan.

[0026] A sensor test / impedance check can be triggered using a push button.

[0027] Light-emitting diodes can be used in a sensor test / impedance check to determine whether and which electrode is applied correctly or incorrectly.

[0028] Furthermore, the device according to the invention indicates whether the battery is currently being charged by means of a yellow LED in the battery pack next to the battery symbol. The state of charge can also be queried via the software, since capacity monitoring is integrated into the battery.

[0029] The stored data can be transferred to a PC via the converter box, which incorporates galvanic isolation. The battery can also be charged via the converter box using the included power adapter. A battery module can also be charged when not installed in the device.

[0030] Another aspect of the device according to the invention is the modular concept of the sensors. According to the invention, additional sensors can be adapted to the handset. For this purpose, a main processor and several subprocessors are provided in the handset. The number of subprocessors is expandable. The subprocessors serve to register the measured values ​​supplied by the sensors, while the main processor manages the communication, timing coordination, and configuration of the subprocessors. This allows the required measured values ​​to be supplemented as needed by adding suitable sensors and corresponding subprocessors. Free connection slots are provided in the handset for this purpose.

[0031] According to the invention, it is provided that at least one EOG and / or one EEG sensor can be supplemented with a corresponding auxiliary sensor.

[0032] The device already has free slots for auxiliary processors, which can be connected to sensor slots also provided in the housing.

[0033] The data transmitted during the measurement are stored and visualized. The data read in after the measurement are automatically analyzed according to time and value criteria, and the occurrence of respiratory disturbances is recorded.

[0034] The software can perform the following automated analyses: • PLM analysis • Snoring analysis • Cardiorespiratory analysis • Arousal Analysis • Sleep stage analysis

[0035] Based on the analysis results and the signals presented, the results can be evaluated according to definable criteria.

[0036] Fig.Figure 5 shows in the left part of the drawing an application with a respiratory flow snoring sensor (16) and in the right part of the drawing an application for pressure measurement in the area of ​​a ventilation mask. Fig. Figure 6 shows an application for data acquisition from a breath flow mouth sensor (27). Further applications are used for the acquisition and recording of measurement data from the breath flow snoring nasal cannula (22) and the pulse oximetry sensor (34).

[0037] Fig.Figure 7 shows the attachment to the patient. To attach the device according to the invention to the patient, the strap is first pulled through the upper eyelet a and then through the side eyelet b of the device. The resulting strap loop is hung over the patient's left shoulder. The short connecting piece with the snap fastener is pulled through the remaining free eyelet c. The strap is closed with the buckle. By adjusting the hook-and-loop fasteners, the strap can be adjusted to the body circumference. The strap is made of a skin-friendly, elastic loop tape.

[0038] The Fig. Figure 8 shows by way of example how the device according to the invention is connected to a PC via a box for galvanic isolation. The charging of the device's batteries also takes place via the box.

[0039] The nasal cannula, which measures airflow and snoring, uses a pressure sensor integrated into the device according to the invention to detect airflow and snoring. Inspiration is registered via the generated negative pressure, and expiration via the generated positive pressure. Snoring creates pressure fluctuations in the nasal openings, which are also recorded. With the mouth closed, the pressure measurement is more sensitive to slight flow limitations than thermal measurement. It is independent of ambient temperature and additionally allows for the visual assessment of the flow contour over time. Signals may be weakened during mouth breathing. Therefore, the simultaneous use of the mouth-flow sensor is an alternative.

[0040] The pulse oximetry sensor measures pulse oximetric signals, blood oxygen saturation, and pulse rate. Optionally, according to the invention, sensors are used that alternatively and / or additionally enable the determination of the concentration of hemoglobin (cHb), oxyhemoglobin (HbO2), deoxygenated hemoglobin (HbDe), carboxyhemoglobin (HbC0), methemoglobin (cMetHb), sulfhemoglobin (HbSulf), bilirubin, and glucose. For this purpose, the sensors have at least one light source that alternatively and / or additionally emits the following wavelengths, selected from the group: 150 nm ± 15%, 400 nm ± 15%, 460 nm ± 15%, 480 nm ± 15%, 520 nm ± 15%, 550 nm ± 15%, 560 nm ± 15e, 606 nm ± 15%, 617 nm ± 15%, 620 nm ± 15%, 630 nm ± 15%, 650 nm ± 15%, 660 nm ±, 705 nm ± 15%, 710 nm ± 15%, 720 nm ± 10%, 805 nm ± 15%, 810 nm ± 15%, 880 nm ± 15%, 890 nm, 905 nm ± 15%, 910 nm ± 15%, 950 nm ± 15%, 980 nm ± 15%, 980 nm ± 15%, 1000 nm ± 15%, 1030 nm ± 15%, 1050 nm ± 15%, 1100 nm ± 15%, 1200 nm ± 15%, 1310nm ± 15%, 1380nm ± 15%, 1450nm ± 15%, 1600nm ±15%, 1650nm ± 15%, 1670nm ± 15%, 1730nm ± 15%, 1800nm ±15%, 2100 nm ± 15%, 2250 nm ± 15%, 2500 nm ± 15%, 2800 nm ±15%. The main components of the sensor are at least two LEDs and a photodetector. Multiple SpO2 values ​​are preferably determined for each pulse wave (split-pulse wave algorithm).

[0041] The measured pulse rate changes correspond sufficiently accurately to the heart rate changes triggered by a sleep-related apnea syndrome.

[0042] The device according to the invention calculates a quality index for each recorded oxygen saturation value, which characterizes the quality or accuracy of the measured SpO2 value. If the signal is disturbed by movement, the number of values ​​is low. With undisturbed signals, a high number of values ​​are available. Accordingly, a disturbed measurement signal produces a low quality value, while an undisturbed measurement signal results in a high quality value. The quality signal takes on values ​​between 0 and 100%. The quality signal can be helpful in evaluating long-term SpO2 measurements, as it indicates artifacts that occurred during the measurement.

[0043] The thorax and abdomen sensor is used to detect thoracic and abdominal breathing movements.

[0044] Breathing movements cause varying tensile stresses on the sensors in the fastening straps. Due to the piezoelectric effect, the sensors convert these movements into electrical signals. The amplitude of the electrical signals represents the extent of the breathing movements. According to the invention, it is proposed to maintain the amplitude of the sensor signals within a defined range by adaptive gain adjustment. The amplitude must be high enough to allow for signal evaluation.

[0045] The gain must be readjusted, for example, when the position changes, so that the signal always remains within the evaluable amplitude range. However, the controller must not increase the gain rapidly during apneas, which are accompanied by low amplitudes of the electrical signals, as the apneas would otherwise no longer be recognizable as such. Therefore, according to the invention, it is proposed that the gain not be increased and / or only gradually increased for the typical duration of an apnea. The typical duration of an apnea is assumed to be 60 to 90 seconds.

[0046] Starting with signals with low amplitudes, the gain is increased every 10 seconds by the control unit's regulator up to a maximum gain of 64x.

[0047] Fig.Figure 9 shows that the control unit's regulator rapidly reduces the gain as the signal amplitude increases. After one minute, the signal amplitude has dropped. The gain is already below 8x. The gain remains constant for about a minute, then increases more and more rapidly. The regulator increases the gain every 10 seconds. The maximum gain is 64x.

[0048] The signal amplification is adjusted according to the patient's position and / or movements. If the patient is lying supine, the tensile stress on the sensors is the same. If the patient is lying on their side, the tensile stress on the sensors is different. In the case of strong signals, the amplification is rapidly reduced, within seconds.

[0049] The electrophysiological signals are measured using sensors. Gold cup or adhesive sensors can be used for this purpose. • Electroencephalogram (EEG) • Electrooculogram (EOG) • Electromyogram (EMG) • Electrocardiogram (ECG)

[0050] The airflow-snoring sensor (16) detects nasal and oral airflow and snoring sounds. The sensor beads consist of thermistors. They detect airflow via the temperature of the exhaled and inhaled air.

[0051] The microphone registers the patient's snoring sounds.

[0052] The oral airflow sensor is also used to detect oral airflow during diagnosis with the nasal cannula for snoring, therapy monitoring, or therapy adjustment.

[0053] The Pneumo-T adapter (28) is used for therapy monitoring in conjunction with a nasal mask. It records the patient's airflow and snoring during therapy and measures the applied therapy pressure in the mask.

[0054] The pressure-measuring tubes transmit inspiratory and expiratory pressure fluctuations from the mask to the device. Exhaling air creates a slight positive pressure, while inhaling creates a corresponding negative pressure. The number of breaths can be derived from these pressure differences.

[0055] Snoring sounds are measured via rapid pressure changes. The therapeutic pressure is derived from the static component of the pressure signal.

[0056] The Pneumo-T adapter is used in conjunction with xPAP devices for therapy setting and monitoring.

[0057] The Pneumo-T adapter can be used together with the airflow mouth sensor (27) to detect mouth breathing and mouth leaks. The Pneumo-T adapter has a standard cone (ISO 22) for connection to therapy masks.

[0058] The chest sensor is integrated into the device for protection. This sensor detects thoracic breathing movements. It is made of a skin-friendly plastic material. The T-strap is used to attach the chest sensor and the device to the patient's body.

[0059] The abdominal sensor (35), together with the abdominal straps, detects abdominal breathing movements. The sensor is made of a skin-friendly plastic. The abdominal strap is used to attach the abdominal sensor to the patient's body. The sensor is connected to the socket (4) on the device. Table 1: Specifications of the sensors for recording physiological signals. Pneumo-T-adapter Cone according to standard ISO 22 sensor Differential pressure: inspiratory / expiratory pressure fluctuations Effort sensors (thorax, abdomen) Thorax Sensor Integrated sensor in the device method Piezoelectric measurement snoring Airflow snoring sensor Integrated microphone Airflow-anti-snoring nasal cannula Pressure sensor Pneumo-T-adapter Pressure sensor method Logarithmic mean value of the sound pressure signal (microphone) or the pressure fluctuations (pressure sensor) Sensors Touch-proof connectors, according to DIN 42802 1.5 mm Position sensor Position sensor integrated sensor in the device range of values right side, left side, stomach, back, standing Accuracy Position approx. 45° + 15° CPAP / BiPAP / SmartPAP printing Measuring range 0 to 40 hPa Accuracy ±0.6 hPa Pulse oximeter clip sensor SpO2 measuring range 50 to 100% SpO2 accuracy 70% < SpO2 < 100% better than 2% accuracy SpO2 Pulse rate measurement range 30 to 250 bpm Pulse Accuracy ±1 bpm to 2% of the displayed value Signal quality A quality score above 90 is good. Below that, SpO2 values ​​and pulse rate may be unreliable. Airflow Airflow snoring sensor 3 thermistors as sum signal, no measurement function at ambient temperatures between 33 - 38°C Airflow-anti-snoring nasal cannula inspiratory / expiratory pressure fluctuations Airflow mouth sensor A thermistor, no measuring function at ambient temperatures between 33 and 38°C EXG sensors

[0060] The quantity detected by the sensors is voltage. This measurement is taken between two points on the body. Since the measurement is non-invasive and performed on the skin surface, the measurable voltages are very small. For EEG, EOG, and EMG, they are in the microvolt range, and for ECG, in the millivolt range. Like EMGs, ECGs are also recorded bipolarly. The polysomnographic recording of the device according to the invention is based on the Einthoven lead. In the device according to the invention, the reference electrode is the ground electrode at any desired location on the body. Table 1: Specifications of the sensors for recording electrophysiological signals. channel ECG EEG EMG EOG Dynamic range (physical range of values) ± 5mV ±500µV ±250 µV ±500µV resolution 12-bit 12-bit 12-bit 12-bit Lower limit frequency 0.16Hz 0.5Hz 2.7 Hz 0.5Hz Upper limit frequency 100Hz 100Hz 500 Hz 100Hz accuracy ± 3% ± 3% ± 3% ± 3% Input impedance approx. 40 MΩ Perform sensor test

[0061] To check that all sensors are properly connected, a test can be performed after attaching the sensors and devices.

[0062] To check the attachment and / or functionality of the sensors on the patient, an impedance measurement of the applied sensors is performed. To carry out the impedance measurement, a selection switch on the device is activated; button 6 is pressed. An LED is provided for each sensor as an indicator. The LEDs illuminate after the impedance test has been performed. This indicates the quality of the sensor attachment and / or functionality. Preferably, the LEDs indicate at least three levels of sensor attachment and / or functionality—good, medium, poor—to immediately show the user which sensors still need to be readjusted and / or replaced.

[0063] During the sensor test, the LED of the sensor being tested flashes rapidly (4 times per second). If the sensor test result is "good", the LED of the corresponding sensor no longer flashes after the impedance test is complete: The electrode impedance is < 5 kΩ and therefore OK, or a sensor signal is present.

[0064] If the result of the sensor test is "medium", the LED of the corresponding sensor will blink slowly after the impedance test is completed: The electrode impedance, at < 10 kΩ, is not optimal but acceptable. The LEDs blink slowly at 0.5 Hz.

[0065] If the result of the sensor test is "bad", the LED of the corresponding sensor will flash rapidly after the impedance test is completed: The electrode impedance is > 10 kΩ, or there is no sensor signal (check sensor, unacceptable signal quality). The LEDs are flashing rapidly at 1.0 Hz.

[0066] After all configured sensors have been successfully installed, no LEDs on the device according to the invention will light up. Furthermore, the LED on the device according to the invention will not change state once the sensor test is terminated in the software by closing the impedance window.

[0067] During the sensor test, all channels, including effort and pulse oximetry sensors, as well as the thermistor and nasal cannula, are checked for the presence of a signal. If the LED is off, this means: "Sensor is connected and transmitting a (physiological) signal".

[0068] An impedance test always runs through all configured channels once and then displays its result until the window is closed or a new test is started. Combination with therapy systems

[0069] The device according to the invention can be combined with common CPAP, BiLevel, and APAP titration home ventilation therapy systems as a control system. The coupling of both systems is quick and easy via the Pneumo-T adapter, which is inserted between the tubing and the mask. The function of non-medical devices Bluetooth USB adapters

[0070] The Bluetooth-USB adapter allows, for example, data to be received wirelessly online by the device according to the invention, the device to be configured, and application control to be carried out.

[0071] The USB server allows the device according to the invention to be operated via a network. This is necessary in many sleep laboratories when the patient room is located away from the recording room. The USB server, in conjunction with the Bluetooth-USB adapter, allows the device according to the invention to receive data wirelessly, configure the device, and perform application control. The device according to the invention can also be connected via cable using the converter box.

[0072] The CompactFlash® card reader allows the device according to the invention to read the data stored on the CompactFlash® card. The device according to the invention can also be configured using the CompactFlash® card reader, and / or multiple CompactFlash® cards with different configurations can be created. Optional modules

[0073] Supplementary PC software enables the reading and display of therapy control data and the remote adjustment of all mentioned therapy devices via the software, as well as the PC-based evaluation of titration data from a ventilator titration device. Peripheral devices • USB port: supported by Windows, USB 1.1, USB 2.0 • Connections: Three free USB ports for connecting a card reader, USB connection cable for the data logger and Bluetooth® USB adapter • Graphics card: supported by Microsoft Windows, minimum resolution 1024x768, color depth 16 bits • Monitor. 17" CRT monitor or 15" TFT monitor • Mouse Windows-compatible mouse • Printers: supported by Microsoft Windows • Network: Network card, 10 / 100 Mbps (only when using the network USB server) • PC software

[0074] The software for detecting sleep-related breathing disorders offers a suggested evaluation. The assessment of the automatically generated analysis results is the responsibility of the physician. Each time the device according to the invention is reprogrammed, the time in the base unit is synchronized with the PC's system time. If data transmission to the PC is interrupted, the measurement data continues to be stored in the device. In the software, the signals are displayed as a zero line. All data can be read out.

Claims

[1] Device for recording biosignals comprising: a Pneumo-T adapter designed to combine the device with common CPAP, BiLevel and APAP titration home ventilation therapy systems, at least one sensor a mobile control unit connected to the sensor, wherein the mobile control unit is designed as a handheld device attachable to the patient, comprising: a storage unit for data storage, wherein the storage unit is designed as a memory card, at least one interface for data transmission, wherein the interface is designed for connection to peripheral, therapy or diagnostic devices, at least one free connection slot in the area of ​​the handset to add at least one additional sensor, a sensor test device and a signaling means for signaling an output of the sensor test device, a gain adjustment designed to keep the amplitude of the signals from at least one sensor within a predefined range. [2] Device according to claim 1, characterized by that the control unit has at least one accumulator or at least one battery for power supply. [3] Device according to one of claims 1 to 2, characterized by that the control unit is equipped with a charging control. [4] Device according to any one of claims 1 to 3, characterized by that the interface is designed as a USB interface. [5] Device according to any one of claims 1 to 4, characterized by that the sensor and control unit are connected to at least one carrying strap for mobile application. [6] Device according to any one of claims 1 to 5, characterized by that the control unit has a multi-processor system. [7] Device according to claim 6, characterized bythat the multiprocessor system has at least one main processor for coordination and at least one secondary processor for signal processing. [8] Device according to any one of claims 1 to 7, characterized by that at least one free slot is available in the area of ​​the handset for the addition of at least one additional secondary processor. [9] Method for recording biosignals with the device according to claim 1, wherein at least one biosignal is detected by at least one sensor and transmitted to a control unit, wherein the control unit stores biosignal-dependent data on a storage unit, wherein the control unit has at least one interface for data transmission, wherein at least one free connection point for adding at least one further sensor is available in the area of ​​the handset, wherein the control unit comprises a sensor test device and wherein the control unit is equipped with a gain adjustment. [10] Method according to claim 9, characterized by that the control unit is used for data transmission to an evaluation unit. [11] Method according to claim 9 or 10, characterized by that the control unit is used for data transmission to a personal computer. [12] Method according to any one of claims 9 to 11, characterized by , that data in the area of ​​the control unit is processed by a multiprocessor system. [13] Method according to claim 12, characterized by , that coordination is performed by at least one main processor and signal processing by at least one secondary processor. [14] Method according to any one of claims 9 to 13, characterized by , that at least one secondary processor can be added later. [15] Method according to any one of claims 9 to 14, characterized by that the control unit is connected to at least one sensor. [16] Method according to any one of claims 9 to 15, characterized by that the control unit displays to the user the quality of the mounting and / or functionality of the sensors. [17] Method according to any one of claims 9 to 16, characterized by that the control unit performs at least one gain adjustment. [18] Method according to any one of claims 9 to 17, characterized by that the control unit saves the data to a memory card.

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