Patent Application
20200085328
The invention relates to a device for monitoring patient's vital functions such as respiratory and heart rate and changes or arrhythmia thereof.
Various devices for monitoring various vital functions are known in the art. These monitoring devices are used especially in hospitals, mostly in intensive care units, but also in aftercare departments or in nursing homes. Devices are known where there is no need for a direct connection with the patient, which facilitates patient care, as there is no need for patient's cooperation. The direct contact with the patient means various types of for example adhesive sensors or sensors that are inserted into the patient's body.
Majority of the known devices consist of a pad which incorporates one or more sensors of different types. These sensors can detect a change in force applied to the pad, for example by means of various force sensors with offset measurement, strain gauges or sensors employing piezoelectric effect. Furthermore, the sensors can also detect vibrations of the bed-deck caused by the patient, for example, by using various MEMS (micro-electromechanical sensor) sensors. The pad is placed under the area where the patient is located, usually under the mattress.
Device employing appropriately configured strain gauges is described in U.S. Pat. No. 7,699,784. The disadvantage of this solution is that there is often an unwanted reaction to the surrounding forces, due to the configuration of the strain gauges so that the patient's breathing and heartbeat can be recorded.
Devices employing the principle of direct piezoelectric effect are utilized because of their low price and simplicity in measuring high-frequency vital functions, such as heartbeat. An example of such device is disclosed in U.S. Pat. No. 6,984,207. However, these devices are not suitable for measuring low-frequency vital functions, such as breathing.
For measuring low-frequency vital functions, sensors for measuring offset are used, for example, capacity sensors utilizing capacity changes due to change in the size of the air gap between the electrodes, as disclosed, for example, in patent application WO2006131855.
The device can also be as disclosed in patent application WO2010080794 where the pad is filled with fluid, and the pressure sensor senses changes in the pressure caused by breathing and patient's pulse. The problem with this solution is in the production complexity of the special pad filled with liquid.
The device can also employ the video signal evaluation principle as disclosed so in application WO2013027027, where it is possible to evaluate some vital functions on the basis of the light intensity ratio of two different wavelengths reflected from the patients skin. However, this principle is inaccurate and very difficult to perform in poor lighting conditions.
The device can also be formed by mattresses into which the sensor is inserted, as disclosed in U.S. Pat. No. 7,652,581 However, this method is disadvantageous due to the high price of the mattress adapted for this purpose.
Indirect measurement of the patient's vital functions raises sensor accuracy requirements so that they are able to respond also to minor changes caused by breathing or patient's heartbeat and at the same time so that they are not disturbed by undesirable external forces, Meeting these requirements can be achieved by using a combination of sensors, which increases the cost of this device. This problem is partially solved by patent application CZ2013-781, which utilizes a sensor consisting of three conductive electrodes, where one electrode is a piezoelectric sensor and a second electrode together with a third electrode forms a capacity sensor. However, this solution still has high production costs, mechanical complexity and insufficient precision. The disadvantage of this device is also that the piezoelectric sensor is made of a mixture of PolyVinilDene Fluoride and Polyethylene terephthalate material, such sensor has a number of drawbacks in the said application of measuring patient's vital functions. Above all, this material is insufficiently stiff, resulting in the need to regulate the forces applied on the sensor with a rigid, stiffer cover. Furthermore, this sensor needs to be supported from one side by a spring to avoid excessive vibration. The piezoelectric sensor also has a disadvantage in the electromechanical properties of used material, with an elongation of 1% there is a charge in the order of Coulomb units which does not allow sufficient accuracy of either measuring vital functions, such as heartbeat and breathing, or detecting weaker signals such as peristaltic body manifestations.
The abovementioned drawbacks are removed by a device for monitoring patient's vital functions comprising a computing unit and a piezoelectric transducer. The advantage lies in the fact that it further comprises a measuring electrode coupled to a board forming a measuring capacitor together with a piezoelectric transducer. The piezoelectric transducer and the measuring capacitor are electrically connected to the computing unit. The piezoelectric transducer is deformable and is propped against the board on at least two places so that a flexible part of the piezoelectric transducer is located between these places. The place for the bent portion of the piezoelectric transducer is achieved, for example, by the saucer-type shape of the piezoelectric transducer or by placing the piezoelectric transducer on the elevated place of the board or through the hole in the board. This advantage is utilized for mechanical simplification of the design and simultaneously for reduction of the failure rate.
Preferably it is utilized that the piezoelectric transducer comprises a first electrode and a second electrode and a piezoelectric element formed by piezoelectric material located therebetween. The first electrode and the second electrode are electrically connected with the computing unit. In a preferred embodiment, the piezoelectric element is formed by piezoceramics.
Preferably it is utilized that the second electrode has a circular shape.
Preferably it is utilized that the measuring electrode forms together with the first electrode or the second electrode the measuring capacitor.
Preferably it is utilized that it further comprises a printed circuit board. The computing unit, the piezoelectric transducer and the measuring capacitor are located on the printed circuit board.
Preferably it is utilized that the second electrode or the first electrode is on two places of the perimeter of the area adjoining the printed circuit board attached so that each attachment allows the deformation of the piezoelectric transducer.
Preferably it is utilized that it further includes a comparator capacitor. The comparator capacitor is electrically connected with the computing unit.
Preferably it is utilized that the comparator capacitor comprises a first comparator electrode and a second comparator electrode. The first comparator electrode and the second comparator electrode are electrically connected with the computing unit.
Preferably it is utilized that it further includes a sampling capacitor. The sampling capacitor is electrically connected with the computing unit.
Preferably it is utilized that it further includes a shielding electrode of the measuring capacitor. The shielding electrode of the measuring capacitor is electrically connected with the computing unit. The shielding electrode of the measuring capacitor has the same electrical potential as the measuring electrode. In a preferred embodiment, it also includes a shielding electrode of the comparator capacitor. The shielding electrode of the measuring capacitor is electrically connected to the computing unit. The shielding electrode of the comparator capacitor has the same electrical potential as the first comparator electrode or the second comparator electrode.
Preferably it is utilized that it further comprises the printed circuit board. The shielding electrode of the measuring capacitor, the shielding electrode of the comparator capacitor, the comparator capacitor and the sampling capacitor are located on the printed circuit board.
It is preferably utilized that the shielding electrode of the measuring capacitor is located opposite of the measuring electrode and the shielding electrode of the comparator capacitor is located opposite of the first comparator electrode or the second comparator electrode.
An exemplary embodiment of the invention is a device 21 for monitoring patient's vital functions according to
The piezoelectric transducer 8 utilized here for the purpose of measuring vital functions is a component for generating sound, namely an electro-acoustic transducer used in watches, as a siren or as a buzzer. The piezoelectric transducer has suitable mechanical-deformative properties for measuring vital functions, which means that springs and additional members transferring their deformations caused by movements associated with patient's vital functions to the measuring element are not necessary in comparison with prior art devices, thus achieving low production costs, higher measuring accuracy, and simplicity of the entire device 21. A semiconductor component and a circuit utilized for measuring capacity in touchscreen displays (charge transfer technology/method) are utilized in measuring capacity with this component and another measuring (static) electrode 4. A specific exemplary embodiment is described below.
In the exemplary embodiment, the device 21 is on the side of the piezoelectric transducer 8 covered by, for example, a plastic diaphragm which protects the device 21 against water and dust and at the same time also removes the mechanical resonance oscillation of the device 21. The device 21 is on the side opposite of the piezoelectric transducer 8 covered by for example plastic foil which ensures the minimum height of the entire device 21. The plastic film may be replaced by any flexible or movable cover which ensures the transfer of forces to the piezoelectric transducer 8 without its stiffness significantly affecting the resulting force being transmitted to the piezoelectric transducer 8. The device 21 for monitoring patient's vital functions may be adapted for insertion into the pad. The pad can be stored, for example, between the mattress and the bed frame, in the mattress or between the mattress and the patient's body. The device may also be adapted for a direct placement on the bed frame and for detachable locking, for example, with a snap fastener.
The piezoelectric transducer 8 consists of the piezoelectric element 1 from piezoceramics, the first electrode 25 and the second electrode 2. Piezoceramics are for example piezoceramic materials based on lead zirconate titanate [Pb[ZrxTi1-x]O3 with 0≤x≤1] or sodium bismuth titanate [NaBi(TiO3)2] or other piezoceramic material. By using such material, the required electromechanical properties are achieved, namely generation of charge in range of 130-930 pC/N. The piezoelectric element 1 is located between the first electrode 25, for example, from silver, optionally from alloys with similar electrical properties, and the second electrode 2. The piezoelectric transducer 8 may have different shapes, such as a circle, a triangle, square, or other shapes. A preferred shape is the circular shape, which ensures the most uniform decomposition of forces. The shape of the piezoelectric transducer 8 is usually a circle delimited in its height dimension by two parallel planes. Preferably, form modification of the piezoelectric transducer 8 can be utilized, when its center is pressed in the direction of axis perpendicular to one of the delimiting planes and a board-like shape emerges, where the center is located in one plane and in parallel plane lie the borders of the piezoelectric transducer 8. The board-like shape is best illustrated by the shape of the second electrode 2 (or the entire piezoelectric transducer 8) in
The comparator capacitor 9 consists of the first comparator electrode 26, the first comparator electrode 26 can be made, for example, of brass, aluminum, copper. The first comparator electrode 26 is located on the plating 3 for electrical connection with the ground. The comparator capacitor 9 further consists of a second comparator electrode 5. The second comparator electrode 5 is located on the printed circuit board 7 and forms an electrode with higher electrical potential: The dielectric of the comparator capacitor 9 is formed by an air gap. On the opposite side of the printed circuit board 7 opposite of the second comparator electrode 5 is located the shielding electrode 27 of the comparator capacitor 9. The shielding electrode 27 of the comparator capacitor 9 has the same electrical potential as the comparator electrode 5 and together they can form a shielding capacitor 24 which provides resistance to external influences for example by the approximation of metal material.
The computing unit 10 combines piezoelectric voltage measurement and capacity measurement functions, for example, by means of charge transfer technology. Piezoelectric element 1 is connected to the computing unit 10 through a charge amplifier. Furthermore, the measuring capacitor 23, the comparator capacitor 9, the shielding capacitor 24 and the sampling capacitor 11 are connected to the computing unit 10. The use of the measuring capacitor 23 and the comparator capacitor 9 causes resistance to changes in the measuring conditions such as temperature or humidity.
Furthermore, a method for monitoring patient's vital functions according to the above-mentioned exemplary embodiment is described. Heartbeat, breath and other vital functions of the patient, for example peristalsis, generate forces transmitted to the device 21 for monitoring patient's vital functions. With respect to the construction of the device 21, it is ensured that the vital functions of the patient are measurable without the need for permanent connection of the device 21 with the patient's body, for example by means of gluing or implanting. The device 21 is capable of measuring patent's vital functions in contact with the skin of the patient, but also in contact with patient's clothing, mediated through the mattress on which the patient is placed, or through the pad in which the device 21 for monitoring vital functions may be located. The measuring capacitor 23 and the comparator capacitor 9 are used to measure slowly changing forces generated by, for example, breathing. During breathing, due to the applied forces, deflection of the central portion of the second electrode 2 (and therefore to the entire piezoelectric transducer 8) occurs, and thus also change in the air gap between the second electrode 2 and the measuring electrode 4. Due to the construction where the piezoelectric transducer 8 is attached to the board by one of the electrodes, a non-mediated deflection of the piezoelectric transducer 8 without the need for additional force transmitting components is enabled. The size of the air gap between the first comparator electrode 26 and the second comparator electrode 5 is independent of the action of the forces. The change in the capacity of the measuring capacitor 23 is dependent both on the varying air gap size and on the change of permittivity of the air gap. The change in the capacity of the comparator capacitor 9 is dependent only on change in permittivity of the air gap. The capacity of the measuring capacitor 23 and the capacity of the comparator capacitor 9 ratio will remove the dependence of the capacitance change on dielectric permittivity and thereby the independence of changing the measuring conditions.
Capacity changes are evaluated for example by charge transfer technology. The charge transfer technology operates on the principle of charging the capacitor and subsequent transfer of the accumulated charge into the sampling capacitor 11, wherein the number of accumulated charge transfers into the sampling capacitor is counted, until the voltage at the sampling capacitor 11 reaches the same value as the stable reference voltage. It is clear to a person skilled in the art that other methods of measuring capacity can be utilized, for example, the resonance method. In order to measure fast-changing forces caused for example by pulse, a direct piezoelectric effect of the piezoelectric material is used, where by deformation of the piezoelectric material due to external forces, a charge which is through the charge amplifier transferred to the computing unit 10 is generated where the voltage is evaluated. The output data are then transmitted via the data wire 22 to the control unit 20. The computing unit 10 can be provided as a microprocessor, its location on the printed circuit board 7 ensures a protection of the signal because the distance of the transmitted non-digital signal is very small.
Further, a method for communication of the measuring elements A1 to AN 13, 14, 15 which may be devices for monitoring vital functions of a patient 21 or sensors of other type according to
| Number | Date | Country | Kind |
|---|---|---|---|
| PV 2016-366 | Jun 2016 | CZ | national |
| Filing Document | Filing Date | Country | Kind |
|---|---|---|---|
| PCT/CZ2017/000041 | 6/22/2017 | WO | 00 |
