KR102182600B1 - Pulse sensing module, blood pressure calculation module, blood pressure measuring device and method for manufacturing pulse sensing module - Google Patents

Abstract

A blood pressure calculation module according to an embodiment of the present invention is a module for calculating at least one of a systolic pressure, a diastolic pressure, and a blood pressure change amount using a pulse voltage signal using a piezoelectric effect, A signal preprocessing unit receiving the voltage signal to amplify the amplitude of the voltage signal and filter noise; A converter configured to digitally convert the voltage signal preprocessed by the signal preprocessor and output it; And a control unit for calculating at least one of the systolic blood pressure, the diastolic blood pressure, and the blood pressure change amount based on the voltage signal converted by the conversion unit, wherein the control unit includes, in each of the pulse signals for a preset time period. After extracting the maximum voltage value (V _Max ) and the minimum voltage value (V _Min ) of the corresponding voltage signal, at least one of the systolic blood pressure, the diastolic blood pressure, and the blood pressure change amount is calculated based on these. I can.

Description

Pulse sensing module, blood pressure calculating module, blood pressure measuring device, and manufacturing method of pulse sensing module TECHNICAL FIELD [Pulse sensing module, blood pressure calculation module, blood pressure measuring device and method for manufacturing pulse sensing module}

The present invention relates to a pulse sensing module, a blood pressure calculating module, a blood pressure measuring device, and a method of manufacturing a pulse sensing module, and more particularly, a pulse sensing module, a blood pressure calculating module, and a blood pressure that allow blood pressure to be measured by a piezoelectric effect through a piezoelectric material It relates to a measuring device and a method of manufacturing a pulse sensing module.

In recent years, the standard of living and health consciousness are increasing, so interest and demand for health check-ups are increasing.

In general, for basic medical examinations, blood pressure, pulse waves, electrocardiogram, and body fat are measured and used as basic data.

To this end, each clinic is equipped with a sphygmomanometer for measuring blood pressure, an electrocardiogram measuring device for measuring an electrocardiogram, a body fat measuring device for measuring body fat, a pressurized pulse wave meter for measuring pulse waves, and a volume pulse wave meter for measuring blood flow. .

Among them, as disclosed in Korean Patent Registration No. 10-1059528, the sphygmomanometer for blood pressure measurement was a method of wrapping an armband-shaped compression part on the upper arm of the test subject and then tightening it to fit around the upper arm.

However, this type of blood pressure measurement caused inconvenience in that, when the subject measures the blood pressure by himself/herself, the compression part in the form of an armband must be tightened with one hand.

In addition, recently, the space into which the upper arm is inserted is fixedly formed in a circular shape, and a blood pressure measuring device is used in which the pressure arm automatically swells up and tightens the upper arm when the subject presses the button after inserting the upper arm into the circular space. have.

However, since such a blood pressure measuring device has to insert the upper arm into the circular space, the distance to which the testee's arm must be moved is increased, causing discomfort, and in the case of the test subject with discomfort in the elbow or shoulder, the body is not a joint. Since the arm must be inserted by moving the whole, this also has a problem that it is inconvenient to measure.

Therefore, there is an urgent need to develop a blood pressure measuring device that minimizes discomfort of a test subject in blood pressure measurement and allows it to be accurately measured in a simple manner.

An object of the present invention is to enable blood pressure measurement through the piezoelectric effect of a piezoelectric material on the pulse, and at the same time, a pulse sensing module for improving the accuracy of blood pressure measurement by clearly defining the relationship between the voltage signal due to the piezoelectric effect and the blood pressure. It is to provide a method of manufacturing a calculation module, a blood pressure measuring device, and a pulse sensing module.

A blood pressure calculation module according to an embodiment of the present invention is a module for calculating at least one of a systolic pressure, a diastolic pressure, and a blood pressure change amount using a pulse voltage signal using a piezoelectric effect, A signal preprocessing unit receiving the voltage signal to amplify the amplitude of the voltage signal and filter noise; A converter configured to digitally convert the voltage signal preprocessed by the signal preprocessor and output it; And a control unit for calculating at least one of the systolic blood pressure, the diastolic blood pressure, and the blood pressure change amount based on the voltage signal converted by the conversion unit, wherein the control unit includes, in each of the pulse signals for a preset time period. After extracting the maximum voltage value (V _Max ) and the minimum voltage value (V _Min ) of the corresponding voltage signal, at least one of the systolic blood pressure, the diastolic blood pressure, and the blood pressure change amount is calculated based on these. I can.

The control unit of the blood pressure calculation module according to an embodiment of the present invention calculates a maximum voltage average value (V _Max , _Avg ) that is an average value of the maximum voltage value (V _Max ) extracted from the voltage signal for each of the pulse signals. And calculating the average voltage change amount (V _Avg ), which is an average value of the difference between the maximum voltage value (V _Max ) and the minimum voltage value (V _Min ) extracted from the voltage signal for each of the pulse signals, It may be characterized in that at least one of the systolic blood pressure, the diastolic blood pressure, and the blood pressure change amount is calculated.

The control unit of the blood pressure calculation module according to an embodiment of the present invention, based on a correlation based on big data analysis, the maximum voltage average value (V _Max , _Avg ) and the voltage change amount average value (V _Avg ), respectively It may be characterized in that the systolic blood pressure and blood pressure change amount (P) are calculated from.

The correlation between the maximum voltage average value (V _Max , _Avg ) and the systolic blood pressure (P _systolic ) based on the big data analysis of the blood pressure calculation module according to an embodiment of the present invention satisfies the following <Condition 1> It can be characterized by that.

<Conditional Expression 1>

Here, P _systolic is the systolic blood pressure, V _Max and _Avg are the maximum voltage average values, and α and β are constants derived by big data analysis.

The correlation between the average voltage change amount (V _Avg ) and the blood pressure change amount (P) based on the big data analysis of the blood pressure calculation module according to an embodiment of the present invention satisfies the following <Condition 2> You can do it.

<Conditional Expression 2>

Here, P is the blood pressure change amount, V _Avg is the average voltage change amount, and γ and δ are constants derived by big data analysis.

The control unit of the blood pressure calculation module according to an embodiment of the present invention may be characterized in calculating a diastolic blood pressure (P _diastolic ) by subtracting a blood pressure change amount (P) from the systolic blood pressure (P _systolic ).

A blood pressure measuring device according to another embodiment of the present invention is a device that is attached to the skin to measure at least one of a systolic pressure, a diastolic pressure, and a blood pressure change amount, comprising: a blood pressure calculation module; And a pulse sensing module capable of bending to correspond to a curved skin surface of the human body to generate the voltage signal by the piezoelectric effect in response to each of the pulse signals.

A blood pressure measuring device according to another embodiment of the present invention includes: a bending module to which the pulse sensing module and the blood pressure calculating module are attached and bendable so that the blood pressure measuring device is in close contact with the curved skin surface of the human body; It may be characterized in that it further comprises.

According to the method of manufacturing a pulse sensing module, a blood pressure calculating module, a blood pressure measuring device, and a pulse sensing module according to the present invention, it is possible to measure blood pressure through a piezoelectric effect of a piezoelectric material on a pulse, thereby providing convenience to a subject.

In addition, it is possible to improve the accuracy of blood pressure measurement by clearly defining the relationship between the voltage signal due to the piezoelectric effect and the blood pressure.

In addition, the blood pressure measuring device according to the present invention can be manufactured in a patch or band type, so that accurate blood pressure measurement is possible despite the curved skin characteristics of the human body and human activity, and at the same time, the size can be miniaturized to maximize the utilization width. .

1 is a schematic perspective view showing a blood pressure measuring device according to an embodiment of the present invention and a view for explaining a situation in which the blood pressure measuring device is worn on a wrist and used to measure blood pressure.
2 is a block diagram illustrating a blood pressure measuring apparatus according to an embodiment of the present invention.
Figure 3 is a schematic perspective view showing a pulse sensing module according to the present invention.
4 is a flowchart illustrating a method of manufacturing a pulse sensing module according to the present invention.
5 to 13 are views for explaining a method of manufacturing a pulse sensing module according to the present invention.
14 is a block diagram illustrating a blood pressure calculation module according to the present invention.
15 is a voltage signal graph over time showing a state in which a voltage signal is amplified and filtered by a blood pressure calculation module according to the present invention.
16 is a graph for explaining the correlation between the maximum voltage average value (V _Max , _Avg ) and the systolic blood pressure (P _systolic ) based on big data analysis.
17 is a graph for explaining the correlation between the average voltage change amount (V _Avg ) and the blood pressure change amount (P) based on big data analysis.
18 is a flowchart illustrating a method of measuring blood pressure by a blood pressure measuring device according to an embodiment of the present invention.

Hereinafter, specific embodiments of the present invention will be described in detail with reference to the drawings. However, the spirit of the present invention is not limited to the presented embodiments, and those skilled in the art who understand the spirit of the present invention can add, change, or delete other elements within the scope of the same idea. Other embodiments included within the scope of the inventive concept may be easily proposed, but it will be said that this is also included within the scope of the inventive concept.

In addition, components having the same function within the scope of the same idea shown in the drawings of each embodiment will be described with the same reference numerals.

1. Overview of blood pressure measuring devices

1 is a schematic perspective view showing a blood pressure measuring device according to an embodiment of the present invention and a view for explaining a situation in which the blood pressure measuring device is worn on a wrist and used to measure blood pressure, and FIG. 2 is an embodiment of the present invention A block diagram illustrating a blood pressure measuring apparatus according to an example.

1 and 2, the blood pressure measuring apparatus 100 according to an embodiment of the present invention is attached to the skin so that at least one of systolic pressure, diastolic pressure, and blood pressure change amount is measured. As a device, it may be implemented as a patch type or a band type attached to a place in the human body where a pulse can be detected.

The blood pressure measurement device 100 may be implemented in a band type that can be worn on a wrist as shown in FIG. 1(b). Hereinafter, the case where the blood pressure measurement device 100 is implemented in a band type is an example. Listen and explain.

The blood pressure measuring apparatus 100 may measure blood pressure using a voltage signal generated due to mechanical pressure caused by a pulse, and may include a pulse sensing module 110 for implementing such a piezoelectric effect.

The pulse sensing module 110 may sense a pulse signal of a test subject to generate a voltage signal corresponding to the pulse signal, and the voltage signal is amplified, filtered, and digitized to provide systolic pressure and diastolic pressure. pressure) and blood pressure change.

The above-described process for the voltage signal may be performed by the blood pressure calculation module 120, and the blood pressure calculation module 120 may be electrically connected to the pulse sensing module 110 for analysis of the voltage signal. have.

The blood pressure calculation module 120 may calculate a systolic blood pressure, a diastolic blood pressure, and a blood pressure change amount from the voltage signal through a conditional expression derived based on big data analysis.

Meanwhile, the blood pressure measuring apparatus 100 may include a battery module 130 for driving the blood pressure calculating module 120.

The battery module 130 may include a battery such as a lithium battery capable of supplying power and capable of charging or discharging, but is not limited thereto, and any battery capable of driving the blood pressure calculation module 120 Applicable.

The battery module 130 may include a component for charging the battery, and may include, for example, a charger IC for constant current charging.

In addition, the battery module 130 may include a boosting circuit and a converting circuit for implementing it when it is necessary to boost or reduce the output voltage of the battery for driving the blood pressure calculation module 120.

For example, when the output voltage of the battery is 3V or a driving voltage of 5V is required, the battery module 130 may include a boosting circuit for boosting 3V to 5V and a converting circuit for converting 5V to -5V. will be.

On the other hand, the blood pressure measuring device 100 may be implemented in a patch type or a band type as described above and attached to a place where a pulse can be detected. When the attached place is a curved skin surface, the accuracy of blood pressure measurement is improved. It may include a bending module 140 that can be bent so as to be in close contact with the curved skin surface.

The pulse sensing module 110, the blood pressure calculation module 120, and the battery module 130 may be attached to the bending module 140, and the bending module 140 is configured to support the components. It can be an element.

The bending module 140 may be implemented with a rubber material or a synthetic material having flexibility and flexibility that can be bent to wrap around the wrist. For example, the bending module 140 may be formed of polyimide or polyimide. It may be implemented as an ester or the like.

In addition, the bending module 140 may be formed of a material that has a predetermined elasticity and returns to its original state.

Like the bending module 140, the pulse sensing module 110 and the blood pressure calculating module 120 may have a predetermined flexibility, and thus, the blood pressure measuring device 100 according to the present invention is Since it is possible to improve the accuracy of the voltage signal, it is possible to maximize the accuracy of blood pressure measurement.

Meanwhile, in FIG. 1 (a), it is shown that the blood pressure measuring apparatus 100 according to the present invention is provided with a flexible cover, but the cover is not necessarily an essential component, and the bending module 140 is May be provided, and at least one of the pulse sensing module 110, the blood pressure calculation module 120, and the battery module 130 may be exposed.

Hereinafter, the pulse sensing module 110 and the blood pressure calculating module 120, which are components for measuring blood pressure by the blood pressure measuring apparatus 100, will be described in detail.

2. Pulse sensing module and manufacturing method thereof

3 is a schematic perspective view showing a pulse sensing module according to the present invention, FIG. 4 is a flow chart illustrating a method of manufacturing a pulse sensing module according to the present invention, and FIGS. 5 to 13 are pulse sensing modules according to the present invention. It is a figure for demonstrating the manufacturing method of.

First, referring to FIG. 3, the pulse sensing module 110 according to the present invention is a component for generating a voltage signal due to mechanical pressure due to a pulse, and includes a piezoelectric layer 112 and a protective layer 114. can do.

The piezoelectric layer 112 may be a piezoelectric thin film made of a piezoelectric material for generating a piezoelectric effect due to a pulse, and a first electrode line 116a and a second electrode disposed spaced apart from each other on one surface of the piezoelectric layer 112 The electrode line 116b may be formed like a pattern.

The protective layer 114 is a component applied to the piezoelectric layer 112 to protect the piezoelectric layer 112, and a partial region of the first electrode line 116a and the second electrode line 116b It may include openings 114a and 114b to expose some areas of the.

The openings 114a and 114b enable a polling process of applying a high voltage to the first electrode line 116a and the second electrode line 116b to improve the polarity of the piezoelectric material, and the first electrode line (116a) and the second electrode line 116b may be electrically connected to the blood pressure calculation module 120.

The openings 114a and 114b are formed at positions corresponding to the ends of the first electrode line 116a and the end of the second electrode line 116b, respectively, and the second openings 114a and 114b It may include.

The protective layer 114 may be implemented with an epoxy curable by ultraviolet (UV) light, for example, a negative SU-8 series composed of Bisphenol A Novolacs (phenol-formaldehyde)-based Expoy. Can be a photoresist.

The protective layer 114 surrounds an area other than a partial area of the first electrode line 116a exposed through the first opening 114a among the entire area of the first electrode line 116a, and includes the first electrode line 116a. A region other than a partial region of the second electrode line 116b exposed through the second opening 114b among the entire region of the second electrode line 116b may be enclosed.

Meanwhile, the pulse sensing module 110 is bonded to the other surface of the piezoelectric layer 112 so that the shape of the piezoelectric layer 112 is maintained so that it is stably attached to the bending module 140 of the blood pressure measurement device 100. It may include an adhesion medium layer 118.

The adhesion medium layer 118 may be generally implemented as a transparent plastic substrate such as poly(ethyl benzene-1,4-dicarboxylate) or PEN (polyethylene naphthalate).

The adhesion medium layer 118 may be attached to the other surface of the piezoelectric layer 112 through the bonding layer 119, and bendable to be interlocked with the bending of the bending module 140, so that the piezoelectric layer 112 ) May be blocked from being separated from the bending module 140.

The bonding layer 119 may be, for example, a product of a Norland Optical Adhesive (NOA) solution cured by ultraviolet (UV) light, and may be applied by spin coating.

Here, the blood pressure measurement device 100 may be implemented in a patch type or a band type and attached to a place where a pulse can be sensed, and the bending module 140 having flexibility and flexibility even when the place to be attached is a curved skin surface. It can be brought into close contact with the curved skin surface.

In this case, since the adhesion medium layer 118 is also flexible and can be bent, it can be interlocked and bent when the bending module 140 is bent, and thereby the adhesion medium layer 118 is separated from the bending module 140. This may be prevented in advance, and as a result, separation of the piezoelectric layer 112 from the bending module 140 may be prevented in advance.

Hereinafter, a method of manufacturing the pulse sensing module 110 will be described.

Referring to FIG. 4, in the manufacturing method of the pulse sensing module 110, a first step of forming a piezoelectric layer 112 using a piezoelectric material on one surface of the sacrificial substrate 200 (S10 ), the sacrificial substrate ( The second step of separating 200 from the piezoelectric layer 112 (S20), so that the shape of the piezoelectric layer 112 is maintained so that it is stably attached to the bending module 140 of the blood pressure measuring device 100, A third step (S30) of forming an adhesion medium layer 118 on one surface of the piezoelectric layer 112 from which the sacrificial substrate 200 is separated, a first arranged spaced apart from each other on the other surface of the piezoelectric layer 112 A fourth step (S40) of forming the electrode line 116a and the second electrode line 116b, and the first electrode line 116a and the second electrode line 116b to protect the piezoelectric layer 112 A fifth step (S50) of forming a protective layer 114 on the other surface of the formed piezoelectric layer 112 may be included.

Here, the first step (S10) may include forming a stress relief layer (300) (S12) and forming a temporary substrate layer (400) (S14), the fourth Step (S40) is a step of removing the stress reduction layer 300 and the temporary substrate layer 400, which are performed before forming the first electrode line 116a and the second electrode line 116b (S42) It may include.

On the other hand, the manufacturing method of the pulse sensing module 110 is a sixth polling process in which a high voltage is applied to the first electrode line 116a and the second electrode line 116b to improve the polarity of the piezoelectric material. It may further include a step (S60).

Hereinafter, each step will be described in detail with reference to FIGS. 5 to 13, and the drawings are exaggerated for convenience of explanation.

Referring to FIG. 5, first, a first step S10 of forming a piezoelectric layer 112 as a piezoelectric thin film using a piezoelectric material on one surface of the sacrificial substrate 200 may be performed.

The sacrificial substrate 200 may be made of quartz or sapphire, which is transparent and capable of withstanding high temperature heat treatment, and to form the piezoelectric layer 112 by growing a piezoelectric thin film made of a piezoelectric material. It may be a necessary component.

For example, the sacrificial substrate 200 may be implemented with Al ₂ O ₃ based sapphire having a structure similar to the crystal structure of the piezoelectric thin film for growth of the piezoelectric thin film.

The piezoelectric material has a perovskite structure and may be a material such as lead zirconate titanate (PZT), but is not limited thereto.

A method of forming the piezoelectric layer 112, which is a piezoelectric thin film using the piezoelectric material, may be applied to various known methods, for example, DC/RF sputtering, aerosol deposition, sol-gel solution process (after spin coating). Heat treatment), screen/inkjet printing, or the like.

The sacrificial substrate 200 may be separated from the piezoelectric layer 112 which is a piezoelectric thin film by a laser lift-off (LLO) method during the second step (S20), and for this purpose, a transparent substrate through which light can be transmitted. It can be implemented as

Referring to FIG. 6, after forming the piezoelectric layer 112 on one surface of the sacrificial substrate 200, the sacrificial substrate is used to relieve stress caused by at least one of high temperature, high pressure, and impact that may occur in a later step. A step (S12) of forming the stress reduction layer 300 on the other surface opposite to one surface of the piezoelectric layer 112 on which 200) is formed may be performed.

When the second step (S20) of removing the sacrificial substrate 200 is performed, the stress reduction layer 300 causes the piezoelectric layer 112, which is a piezoelectric thin film, to be stressed by mechanical, physical, and thermal external forces due to high temperature, high pressure, and impact. This may be a component for preventing structural or material deformation such as cracks or wrinkles from occurring, resulting in a decrease in piezoelectric properties or inaccuracies in output voltages.

The stress reduction layer 300 may be an epoxy cured by ultraviolet (UV) light and may be Bisphenol A Novolacs (phenol-formaldehyde)-based epoxy, and a thickness of 500 nm or more may be sufficient.

Referring to FIG. 7, when the stress reduction layer 300 is formed, forming a temporary substrate layer 400 on one surface of the stress reduction layer 300 for handling the piezoelectric layer 112 in a later step ( S14) may proceed.

After the temporary substrate layer 400 is separated from the piezoelectric layer 112 by the second step (S20), which is a later step, the thickness of the entire layer except the temporary substrate layer 400 is When the step after the second step (S20) is performed only with this thickness without the temporary substrate layer 400, it is practically impossible to handle the piezoelectric layer 112, which is a piezoelectric film. It is necessary.

Of course, the step of forming the stress reduction layer 300 as a single layer capable of simultaneously implementing the function of the stress reduction layer 300 and the temporary substrate layer 400 (S12) and the temporary substrate layer 400 The step of forming (S14) may be performed as one step.

The temporary substrate layer 400 may be implemented with a material that can be removed by heat or ultraviolet (UV) light.

For example, the temporary substrate layer 400 may be a thermally expandable adhesive or a tape in which an ultraviolet (UV) energy beam expandable adhesive is applied on one or both sides, and the adhesive is easily used by heat or ultraviolet rays (UV). It may have a property of being evaporated by expansion.

The adhesive has a structure in which spherical or other types of particles are included in the matrix material, and the matrix material is polyvinyl alcohol, polyvinyl butyral, polyacrylonitrile, As a thermoplastic material such as polysulfone, it can have a property of melting and expanding by heat and rupture, and the particles present inside have a structure such as isobutene, propane, or pentane As the thermally expandable particles having a, 500 nm to 100 μm is preferred, and may be a single or a combination of at least two or more.

The adhesive as described above may be applied to one or both sides of the tape, and the thickness of the temporary substrate layer 400 may be, for example, 1 to 500 μm.

Referring to FIG. 8, after the stress reduction layer 300 and the temporary substrate layer 400 are formed through the first step S10, the second step of separating the sacrificial substrate 200 from the piezoelectric layer 112 (S20) may proceed.

A method of separating the sacrificial substrate 200 from the piezoelectric layer 112 may be a mechanical peeling method, a chemical etching method, or the aforementioned laser lift-off (LLO) method.

For example, when the method of separating the sacrificial substrate 200 from the piezoelectric layer 112 is a laser lift-off (LLO) method, the sacrificial substrate 200 is implemented as a transparent substrate through which light can be transmitted. , It may be removed by light energy transmitted through the transparent substrate.

Referring to FIG. 9, the piezoelectric layer 112 from which the sacrificial substrate 200 is separated so as to be stably attached to the bending module 140 of the blood pressure measuring device 100 by maintaining the shape of the piezoelectric layer 112 A third step (S30) of forming the adhesion media layer 118 on one side may be performed.

The adhesion media layer 118 may be attached to the other surface of the piezoelectric layer 112 via the bonding layer 119.

The bonding layer 119 may be, for example, a product of a NOA (Norland Optical Adhesive) solution cured by ultraviolet (UV) light, and may be applied by spin coating.

The adhesion medium layer 118 may be flexible and bendable. Accordingly, when the blood pressure measurement device 100 is attached in close contact with the curved skin surface for blood pressure measurement, the bending module 140 having flexibility and flexibility By bending in conjunction with the bending of, the separation of the adhesion medium layer 118 from the bending module 140 can be prevented in advance, and eventually, the separation of the piezoelectric layer 112 from the bending module 140 It can be prevented in advance.

Referring to FIGS. 10 and 11, a fourth step S40 of forming a first electrode line 116a and a second electrode line 116b formed to be spaced apart from each other on the other surface of the piezoelectric layer 112 may be performed. .

Here, as shown in FIG. 10, removing the stress reduction layer 300 and the temporary substrate layer 400 before forming the first electrode line 116a and the second electrode line 116b ( S42) may be performed, which may be performed through a process of applying heat or ultraviolet rays (UV).

When the heat or ultraviolet rays (UV) are applied, the adhesive included in the temporary substrate layer 400 expands and vaporizes to weaken the adhesive strength, and thereafter, the stress reduction layer 300 and the temporary The substrate layer 400 may be removed.

Here, since the stress reduction layer 300 has already been cured, an increase in adhesion with other layers does not occur even when heat or ultraviolet (UV) is applied, and the temporary substrate layer 400 has heat and ultraviolet rays (UV). Even if the adhesive component expands and vaporizes when this is applied, the adhesive strength remains enough to be separated through a physical peeling operation.

The adhesive force of the temporary substrate layer 400 to be separated through a physical peeling operation is greater than the adhesive force of the stress reduction layer 300 adhered to the piezoelectric layer 112, During the phosphorus peeling operation, the stress reduction layer 300 may also be removed at the same time.

However, the removal of the stress reduction layer 300 and the removal of the temporary substrate layer 400 do not necessarily need to be simultaneously performed, and may be performed sequentially.

As shown in FIG. 10, after the stress reduction layer 300 and the temporary substrate layer 400 are removed, as shown in FIG. 11, a first electrode disposed to be spaced apart from each other on the other surface of the piezoelectric layer 112 A line 116a and a second electrode line 116b are formed.

The first electrode line 116a and the second electrode line 116b may be formed in a pattern through a known semiconductor process after applying an electrode material.

The first electrode line 116a and the second electrode line 116b may each include a plurality of parallel lines disposed parallel to a main line, but the arrangement of the lines may be variously changed.

Referring to FIG. 12, after the first electrode line 116a and the second electrode line 116b are formed, the first electrode line 116a and the second electrode line ( A fifth step (S50) of forming the protective layer 114 on the other surface of the piezoelectric layer 112 on which 116b) is formed may be performed.

The protective layer 114 may have a first opening 114a and a second opening 114b to expose an end of the first electrode line 116a and an end of the second electrode line 116b.

Here, the exposed end of the first electrode line 116a and the end of the second second electrode line 116b may enable a polling process performed in a later step, and a blood pressure calculation module for measuring blood pressure ( 120) can be used as a component for electrical connection.

Referring to FIG. 13, when the formation of the protective layer 114 is completed, a polling process of applying a high voltage to the first electrode line 116a and the second electrode line 116b to improve the polarity of the piezoelectric material. Step 6 (S60) may proceed.

The polling process is a process of imparting dipole directionality in the piezoelectric material, and may be performed by applying an electric field of, for example, 100 kV/cm level for at least 2 hours, but is not limited thereto.

As described above, the polling process in the sixth step (S60), that is, application of a high voltage is enabled through the first opening 114a and the second opening 114b of the protective layer 114, and the pulse sensing module 110 ) Is physically sufficiently protected and the polarity efficiency of the piezoelectric layer 112 can be maximized.

In other words, in the case of applying a high voltage, if the protective layer 114 does not exist, electricity is generated due to the effect of the electric field between the electrodes and the electrode is disconnected. However, in the present invention, the first opening ( 114a) and the protective layer 114 having the second opening 114b cancels the effect of the electric field between electrodes, thereby solving the above problem, thereby improving the polarity efficiency of the piezoelectric layer 112 .

When the first step (S10) to the sixth step (S60) are completed as described above, the manufacture of the pulse sensing module 110 constituting the blood pressure measuring device 100 is completed.

3. Blood pressure calculation module

14 is a block diagram illustrating a blood pressure calculation module according to the present invention, and FIG. 15 is a voltage signal graph over time showing a state in which a voltage signal is amplified and filtered by the blood pressure calculation module according to the present invention.

In addition, FIG. 16 is a graph for explaining the correlation between the maximum voltage average value (V _Max , _Avg ) based on big data analysis and the systolic blood pressure (P _systolic ), and FIG. 17 is a voltage based on big data analysis. This is a graph for explaining the correlation between the average change amount (V _Avg ) and the blood pressure change amount (P).

First, referring to FIGS. 14 to 17, the blood pressure calculation module 120 according to the present invention uses a voltage signal generated by a piezoelectric effect provided through an electrically connected pulse sensing module 110 to determine systolic blood pressure, diastolic blood pressure, and It may be a module that calculates at least one of the blood pressure change amount.

The blood pressure calculation module 120 may basically include a flexible printed circuit board, and a chip or the like that performs a function described below may be mounted on the flexible printed circuit board or a circuit may be patterned.

The flexible printed circuit board may be attached to the bending module 140, whereby when the blood pressure measuring device 100 is in close contact with the curved skin surface for blood pressure measurement, the bending module 140 having flexibility and flexibility ) Can be bent in conjunction with the bending.

The electrical connection between the pulse sensing module 110 and the blood pressure calculating module 120 is between the first electrode line 116a exposed through the first opening 114a and the second opening 114b of the protective layer 114. It may be implemented by interconnecting an end portion and an end portion of the second electrode line 116b with a terminal of the flexible printed circuit board using a conductive material, and the conductive material may preferably be a metallic material having a resistance of 10Ω or less.

On the other hand, the blood pressure calculation module 120 receives a voltage signal provided by the pulse sensing module 110, amplifies the amplitude of the voltage signal and filters out noise, the signal preprocessor 122, the signal preprocessor 122 ) On the basis of the conversion unit 124 converting and outputting the voltage signal preprocessed by digital and the voltage signal converted by the conversion unit 124, among the systolic blood pressure, the diastolic blood pressure, and the blood pressure change amount It may include a control unit 126 that calculates at least one.

Here, the signal preprocessing unit 122 may include an amplifying unit 122a and a filtering unit 122b, and the amplifying unit 122a may amplify the voltage signal provided by the pulse sensing module 110. In addition, the filtering unit 124b may filter noise included in the amplified voltage signal.

FIG. 15 illustrates a voltage signal graph over time in a state in which a voltage signal generated due to mechanical pressure due to a pulse is amplified by the amplifying unit 122a and noise is filtered by the filtering unit 122b.

The conversion unit 124 is a component that converts a voltage signal amplified by the amplifying unit 122a and filtered with noise by the filtering unit 122b to digital, and converts the voltage signal from analog to digital to control the control unit 126 ) May be an A/D conversion unit that outputs in the form of a recognizable voltage signal.

On the other hand, the controller 126 may calculate at least one of the systolic blood pressure, the diastolic blood pressure, and the blood pressure change amount based on the voltage signal digitally converted through the conversion unit 124. Explain.

When the test subject wears the blood pressure measuring device 100 on the wrist and requests blood pressure measurement, the pulse sensing module 110 senses the pulse signal for a preset time in response thereto, and calculates a blood pressure signal according to the piezoelectric effect. It is transmitted to the module 120.

Here, the predetermined time may be, for example, 15 seconds as shown in FIG. 15, but is not limited thereto, and may be variously changed.

The control unit 126 may extract a maximum voltage value (V _Max ) and a minimum voltage value (V _Min ) of a voltage signal corresponding to each pulse signal during the preset time, and thereafter, the The maximum voltage average value (V _Max , _Avg ), which is an average value of the maximum voltage value (V _Max ) extracted from a voltage signal, is calculated, and the maximum voltage value (V _Max ) extracted from the voltage signal for each of the pulse signals The average value of the voltage change amount (V _Avg ), which is an average value of the difference between the and the minimum voltage value (V _Min ), is calculated.

<Conditional Equation 1> and <Conditional Equation 2> for calculating the maximum voltage average value (V _Max , _Avg ) and the average voltage change amount (V _Avg ) are as follows.

<Conditional Expression 1>

<Conditional Expression 2>

Here, n is the number of pulse signals, and may be 16 in the case of FIG. 15.

After calculating the maximum voltage average value (V _Max , _Avg ) and the voltage change amount average value (V _Avg ) through the <Conditional Equation 1> and the <Conditional Equation 2>, the control unit 126 performs a correlation based on big data analysis. Based on, the systolic blood pressure (P _systolic ) and the blood pressure change amount (P) are calculated from the maximum voltage average values (V _Max , _Avg ) and the voltage change average values (V _Avg ).

Here, by comparison a relationship between the systolic blood pressure (P _systolic) Big Data analysis for calculating the average maximum of the collected and stored examinee with big data type information voltage (V _{Max, Avg)} and systolic blood pressure (P _systolic) It may be obtained, and FIG. 16 shows the correlation between the average maximum voltage value (V _Max , _Avg ) and the systolic blood pressure (P _systolic ) based on big data analysis for a normal person.

Referring to FIG. 16, in the case of a normal person, the correlation between the maximum voltage average value (V _Max , _Avg ) and the systolic blood pressure (P _systolic ) by big data analysis is as shown in <Conditional Equation 3> below.

<Conditional Expression 3>

V _Max , _Avg = 2.20113 * 10 ^-4 * P _systolic + 0.0033

Therefore, when <Condition 3> is generalized, the correlation between the maximum voltage average value (V _Max , _Avg ) and systolic blood pressure (P _systolic ) can be generalized by <Condition 4> below.

<Conditional Expression 4>

Here, P _systolic is the systolic blood pressure, V _Max and _Avg are the maximum voltage average values, α and β are constants derived from big data analysis, and in the case of a normal person, α is 2.20113*10 ^-4 and β is 0.0033.

In addition, the big data analysis for calculating the blood pressure change amount (P) can be obtained by comparing and analyzing the relationship between the average voltage change amount (V _Avg ) and the blood pressure change amount (P) among the subject information collected and stored in the form of big data. , FIG. 17 shows the correlation between the average voltage change amount (V _Avg ) and the blood pressure change amount (P) by analyzing big data for normal people.

Referring to FIG. 17, in the case of a normal person, the correlation between the average voltage change amount (V _Avg ) and the blood pressure change amount (P) by big data analysis is as shown in <Conditional Equation 5> below.

<Conditional Expression 5>

P(mmHg) = -2196.83 * V _Avg (mV) + 106.82125

Therefore, if <Conditional Equation 5> is generalized, the correlation between the average voltage change amount (V _Avg ) and the blood pressure change amount (P) can be generalized by the following <Conditional Equation 6>.

<Conditional Expression 6>

Here, P is the blood pressure change amount, V _Avg is the average voltage change amount, γ and δ are constants derived by big data analysis, and in the case of a normal person, γ is 2196.83 and δ is 106.82125.

On the other hand, α, β, γ, and δ used in <Conditional Equation 4> and <Conditional Equation 6> may vary according to the characteristics of the subject collected and stored in the form of big data, for example, hypertension, hypotension, disease group, age, It may be a constant that may vary depending on gender.

The control unit 126 may calculate a diastolic blood pressure (P _diastolic ) by subtracting the blood pressure change amount (P) from the systolic blood pressure (P _systolic ) as shown in <Condition 7> below.

<Conditional Expression 7>

As described above, the blood pressure calculation module 120 according to the present invention amplifies and filters the voltage signal due to the piezoelectric effect provided through the pulse sensing module 110 electrically connected, converts it to digital, and performs a series of processing. Finally, systolic blood pressure and diastolic blood pressure are calculated so that the blood pressure of the subject can be measured.

In addition, blood pressure is determined by using the correlation between the maximum voltage average value (V _Max , _Avg ) and systolic blood pressure (P _systolic ) derived by big data analysis, and the correlation between the average voltage change value (V _Avg ) and the blood pressure change amount (P). Because of the measurement, the accuracy of blood pressure measurement can be improved.

Since the blood pressure measurement apparatus 100 according to an embodiment of the present invention may be implemented in a patch type or a band type attachable to the skin, convenience may be provided to the examiner and the examinee in measuring blood pressure.

Meanwhile, the blood pressure measuring apparatus 100 according to the present invention may further include a display module that displays the systolic blood pressure and the diastolic blood pressure calculated by the control unit 126.

In addition, the blood pressure measuring apparatus 100 according to the present invention may further include a device interface to support interfacing with an external device so that the systolic blood pressure and diastolic blood pressure calculated by the control unit 126 are displayed through an external device. have.

4. A method of measuring blood pressure using a blood pressure measuring device and a recording medium in which a program for executing this method is recorded

18 is a flowchart illustrating a method of measuring blood pressure by a blood pressure measuring device according to an embodiment of the present invention.

Referring to FIG. 18, in the blood pressure measurement method by the blood pressure measuring device according to an embodiment of the present invention, when a test subject wears the blood pressure measuring device 100 on a wrist and requests blood pressure measurement, the pulse sensing module 110 ) Sensing the pulse signal for a preset time and generating a voltage signal according to the piezoelectric effect (S100), the maximum voltage value (V _Max ) and the minimum of the voltage signal corresponding to each pulse signal during the preset time The second step (S200) of extracting a voltage value (V _Min ), a maximum voltage average value (V _Max , _Avg ) that is an average value of the maximum voltage value (V _Max ) extracted from the voltage signal for each of the pulse signals A third calculating and calculating the average value of the voltage change amount (V _Avg ) that is an average value of the difference between the maximum voltage value V _Max and the minimum voltage value V _Min extracted from the voltage signal for each of the pulse signals Step (S300), based on the correlation based on big data analysis, the systolic blood pressure (P _systolic ) and the blood pressure change amount from the maximum voltage average value (V _Max , _Avg ) and the voltage change average value (V _Avg ), respectively The fourth step (S400) of calculating (P), the fifth step (S500) of calculating the diastolic blood pressure (P _diastolic ) by subtracting the blood pressure change amount (P) from the systolic blood pressure (P _systolic ), and the calculated result value It may include a sixth step (S600) of outputting.

Here, the second step (S200) to the fifth step (S500) may be performed by the control unit 126 of the blood pressure calculation module 120, and the sixth step (S600) may be performed by a display module or an external device. I can.

In addition, before the second step (S200), a step of amplifying and filtering a voltage signal due to a piezoelectric effect provided through the pulse sensing module 110, and then converting the voltage to digital may be performed.

Meanwhile, each step of the above-described blood pressure measurement method can be implemented as a computer-readable code on a computer-readable recording medium. The computer-readable recording medium includes all types of recording devices that store data that can be read by a computer system. Examples of computer-readable recording media include ROM, RAM, CD-ROM, magnetic tape, floppy disk, optical data storage, etc., and are implemented in the form of carrier waves (for example, transmission through the Internet). Also includes. In addition, the computer-readable recording medium can be distributed over a computer system connected through a network to store and execute computer-readable codes in a distributed manner.

In the above, the configuration and features of the present invention have been described based on the embodiments according to the present invention, but the present invention is not limited thereto, and various changes or modifications can be made within the spirit and scope of the present invention. It will be apparent to those skilled in the art, and therefore, such changes or modifications are found to belong to the appended claims.

100: blood pressure measuring device
110: pulse sensing module
120: blood pressure calculation module
130: battery module
140: bending module

Claims (8)

In a blood pressure calculation module for calculating at least one of a systolic pressure, a diastolic pressure, and a blood pressure change amount using a pulse voltage signal using a piezoelectric effect,
A signal preprocessing unit receiving the voltage signal to amplify the amplitude of the voltage signal and filter noise;
A converter configured to digitally convert the voltage signal preprocessed by the signal preprocessor and output it; And
And a control unit for calculating at least one of the systolic blood pressure, the diastolic blood pressure, and the blood pressure change amount based on the voltage signal converted by the conversion unit, and
The control unit,
After extracting the maximum voltage value (V _Max ) and the minimum voltage value (V _Min ) of the voltage signal corresponding to each pulse signal for a preset time, based on this, at least one of the systolic blood pressure, the diastolic blood pressure, and the blood pressure change amount Yields one,
The maximum voltage average value (VMax, Avg), which is an average value of the maximum voltage value VMax extracted from the voltage signal for each of the pulse signals, is calculated, and the maximum voltage extracted from the voltage signal for each of the pulse signals By calculating the average value of the voltage change amount VAvg, which is an average value of the difference between the value VMax and the minimum voltage value VMin, at least one of the systolic blood pressure, the diastolic blood pressure, and the blood pressure change amount is calculated,
Based on the correlation based on big data analysis, the systolic blood pressure and blood pressure change amount (P) are calculated from each of the maximum voltage average value (VMax, Avg) and the voltage change amount average value (VAvg),
The correlation between the maximum voltage average value (VMax, Avg) and the systolic blood pressure (Psystolic) based on the big data analysis,
A blood pressure calculation module, characterized in that it satisfies the following <Condition 1>.

<Conditional Expression 1>

Here, Psystolic is the systolic blood pressure, VMax,Avg are the maximum voltage average values, and α and β are constants derived by big data analysis.
delete delete delete The method of claim 1,
The correlation between the average voltage change amount (V _Avg ) and the blood pressure change amount (P) based on the big data analysis is,
A blood pressure calculation module, characterized in that it satisfies the following <Condition 2>.

<Conditional Expression 2>

Here, P is the blood pressure change amount, V _Avg is the average voltage change amount, and γ and δ are constants derived by big data analysis.
The method of claim 5,
The control unit,
A blood pressure calculation module, characterized in that the diastolic blood pressure (P _diastolic ) is calculated by subtracting the blood pressure change amount (P) from the systolic blood pressure (P _systolic ).
In the blood pressure measurement device that is attached to the skin to measure at least one of systolic pressure, diastolic pressure, and blood pressure change amount,
A blood pressure calculation module according to claim 1; And
And a pulse sensing module capable of bending to correspond to a curved skin surface of the human body to generate the voltage signal by the piezoelectric effect in response to each of the pulse signals.
The method of claim 7,
And a bending module to which the pulse sensing module and the blood pressure calculation module are attached and bendable so that the blood pressure measurement device is closely attached to the curved skin surface of the human body.

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