KR20160069399A - An ultrasonic transducer for moxibustion therapy - Google Patents

An ultrasonic transducer for moxibustion therapy Download PDF

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Publication number
KR20160069399A
KR20160069399A KR1020140175323A KR20140175323A KR20160069399A KR 20160069399 A KR20160069399 A KR 20160069399A KR 1020140175323 A KR1020140175323 A KR 1020140175323A KR 20140175323 A KR20140175323 A KR 20140175323A KR 20160069399 A KR20160069399 A KR 20160069399A
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KR
South Korea
Prior art keywords
bonding layer
front bonding
ultrasonic
moxibustion
piezoelectric element
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KR1020140175323A
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Korean (ko)
Inventor
김기복
류연희
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한국표준과학연구원
한국 한의학 연구원
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Priority to KR1020140175323A priority Critical patent/KR20160069399A/en
Publication of KR20160069399A publication Critical patent/KR20160069399A/en

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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N7/00—Ultrasound therapy
    • A61N7/02—Localised ultrasound hyperthermia

Abstract

The present invention relates to an ultrasonic transducer for moxibustion therapy which can be heated and maintained at a predetermined temperature in a tissue under the skin by contacting the skin without using moxibustion, And a second front bonding layer bonded to a surface of the front bonding layer and a surface of the first front bonding layer bonded to the piezoelectric element, wherein the second front bonding layer includes at least one ultrasonic focusing lens Thereby providing an ultrasound transducer for moxibustion treatment.

Description

[0001] The present invention relates to an ultrasonic transducer for moxibustion therapy,

The present invention relates to a moxibustion treatment technique, and more particularly, to an ultrasonic wave transducer for moxibustion treatment.

In general, the traditional moxibustion treatment depends on the subjective and qualitative treatment of the practitioner, so it can not be quantitative and lacks objectivity. When directly administered to the body, the granulocyte is greatly increased in the white blood cells, resulting in a decrease in the human immune system and a risk of adult disease due to an increase in blood pressure.

In the case of moxibustion treatment, a woman or a child should consider the cosmetic part because it can leave burn scars on the skin tissue. In addition, face burns should be avoided because it is difficult to recover by burning in case of severe burns. Moxibustion and mugwort may cause a toxic reaction if they are moxibusticated in diabetic patients, and may be particularly dangerous for pregnant women. In addition, it suffers from discomfort caused by smoke generated in moxibustion combustion, and especially in the case of respiratory weaknessers, side effects such as difficulty breathing due to smoke generated during moxibustion treatment.

In case of avoiding visiting a oriental medicine clinic due to burn pain felt during moxibustion treatment or moxibustion in a oriental medicine clinic, additional evacuation facilities and personnel for burn prevention are additionally required. There are several methods to stimulate the menstrual blood, such as electrical, physical, magnetic field, and ultrasound. However, there are many cases in which reproducibility and accuracy are not clearly demonstrated.

In recent years, there has been a rapid increase in the market for magnetic field stimulation devices for stimulating deep, deep, and cartilage in addition to low-frequency treatment devices for electrical stimulation used in percutaneous and transcutaneous nerve stimulation, and as a new attempt to overcome the limitations of clinical applications Studies on the stimulation therapy system have been actively conducted.

Therapeutic devices using magnetic fields are mainly used for pain, nerve, and cartilage regeneration treatment. Electric stimulation methods are used for treatment of skin and obesity by applying hyperthermia therapy. Other surgical laser stimulators are on the market. Most of the stimulating devices have been developed mainly for the application in the fields of oriental medicine and cosmetology, and there is a limit to apply them to oriental medicine treatment field.

<Prior Art Literature>

1. Korean Published Patent No. 10-2012-0137793 (2012.12.24)

2. Korean Patent No. 10-1006309 (December 29, 2010)

Disclosure of the Invention It is an object of the present invention to provide an ultrasound transducer for moxibustion treatment capable of heating and maintaining a tissue under the skin at a constant temperature in contact with skin without using moxibustion to solve various problems including the above- The purpose. However, these problems are exemplary and do not limit the scope of the present invention.

According to one aspect of the present invention, there is provided a piezoelectric element comprising a piezoelectric element, a first front bonding layer bonded to at least one surface of the piezoelectric element, and a second front bonding layer bonded to a surface of the first front bonding layer, The ultrasonic transducer for moxibustion treatment is provided with a second front bonding layer and at least one ultrasonic focusing lens is formed on the second front bonding layer.

In the ultrasonic transducer for moxibustion treatment, the acoustic impedance of the first front bonding layer may be larger than the acoustic impedance of the second front bonding layer.

In the ultrasonic transducer for moxibustion treatment, the acoustic impedance of the first front bonding layer may be in the range of 12 to 14 MRayL, and the acoustic impedance of the second front bonding layer may be in the range of 3 to 4 MRayL.

In the ultrasonic transducer for moxibustion treatment, the first front bonding layer may include a borosilicate glass system, and the second front bonding layer may have an acrylic resin system.

In the ultrasonic transducer for moxibustion therapy, the piezoelectric element may have a value of a piezoelectric constant of 600 pC / N or more.

In the ultrasonic transducer for moxibustion treatment, the number and / or size of the ultrasonic focusing lens formed on the second front bonding layer may be changed according to the applied ultrasonic frequency.

In the ultrasound transducer for moxibustion treatment, the ultrasonic frequency may range from 1 to 5 MHz.

The ultrasonic transducer for moxibustion treatment may further have a case including the piezoelectric element, the first front bonding layer, and the second front bonding layer.

According to one embodiment of the present invention as described above, the ultrasonic transducer for moxibustion therapy, which can be heated and maintained at a predetermined temperature in the tissue under the skin in contact with the skin without using moxibustion, can be realized. Of course, the scope of the present invention is not limited by these effects.

1 is a view schematically showing an ultrasonic transducer for moxibustion treatment according to embodiments of the present invention.
2 is a photograph schematically showing a lens for focusing an ultrasonic wave according to the present invention.
FIG. 3 is a graph of the sound pressure distribution analysis of the ultrasonic focusing lens according to the present invention.
4 is a view schematically showing the design of the ultrasonic focusing lens according to the present invention.
5 is a graph illustrating performance of an ultrasonic focusing lens according to the present invention.
6 is a graph of performance evaluation of the ultrasonic transducer for moxibustion treatment according to the present invention.

Hereinafter, embodiments of the present invention will be described in detail with reference to the accompanying drawings. It should be understood, however, that the invention is not limited to the disclosed embodiments, but may be embodied in many different forms and should not be construed as limited to the embodiments set forth herein. Rather, these embodiments are provided so that this disclosure will be thorough and complete, Is provided to fully inform the user. Also, for convenience of explanation, the components may be exaggerated or reduced in size.

1 is a view schematically showing an ultrasonic transducer for moxibustion treatment according to embodiments of the present invention.

The ultrasonic transducer for moxibustion treatment according to embodiments of the present invention may be implemented by including a second front bonding layer formed with a piezoelectric element, a first front bonding layer, and a lens for ultrasonic focusing.

1, a moxibustion therapeutic ultrasound transducer 100 includes a piezoelectric element 10, a first front bonding layer 20 bonded to at least one surface of the piezoelectric element 10, And a second front bonding layer 30 bonded to a surface of the bonding layer 20 opposite to the surface bonded to the piezoelectric element 10. At this time, one or more ultrasound focusing lenses 40 may be formed on the second front bonding layer 30.

The piezoelectric element 10, the first front bonding layer 20 and the second front bonding layer 30 may be included in the inner case 50 and the inner case 50 may be disposed inside the outer case 60 Lt; / RTI &gt;

A signal line 70 may be connected to the upper electrode of the piezoelectric element 10, and a ground line 80 may be connected to the lower electrode of the piezoelectric element 10.

For example, in the ultrasonic transducer for moxibustion therapy according to the present invention, the signal line 70 and the ground line 80 can be connected to the upper and lower portions of the piezoelectric element 10 on which the upper electrode and the lower electrode are deposited. Then, the first front bonding layer 20 can be bonded to the lower portion of the piezoelectric element 10. Then, the second front bonding layer 30 having the ultrasonic focusing lens 40 formed thereon may be bonded to the surface of the first front bonding layer 20 which faces the piezoelectric element 10. At this time, the surface of the second front bonding layer 30 may be bonded to the opposite surface of the surface on which the lens 40 for focusing the ultrasonic waves is formed.

Then, the bonded piezoelectric element 10, the first front bonding layer 20, and the second front bonding layer 30 may be embedded in the inner case 50.

Then, by embedding the inner case 50 in the outer case 60, ultimately, the ultrasonic transducer for moxibustion treatment can be realized. At this time, the outer case 60 may further include a hole through which the signal line 70 and the ground line 80 can pass.

However, the ultrasonic transducer for moxibustion treatment according to the embodiments of the present invention is not limited to this, and may be constructed such that the first front bonding layer 20 and the second front bonding layer 30 are bonded to each other, .

Then, the piezoelectric element 10 to which the signal line 70 and the ground line 80 are connected can be bonded onto the first front bonding layer 20. Then, the inner case 50 may be built in the outer case 60. [

The piezoelectric element 10 may include, for example, a single element on which the upper electrode and the lower electrode are deposited. The piezoelectric element 10 may include a lead zirconate titanate (PZT) ceramics and may include a material having a large piezoelectric constant d 33 indicating a displacement of the piezoelectric element 10 per unit voltage input. In addition, the d 33 value may include a specific value of 600 pC / N or more, for example.

The first front bonding layer 20 may comprise a material that allows ultrasound energy to penetrate the skin tissue as much as possible. Also, the acoustic impedance of the first front bonding layer 20 may include a value larger than the acoustic impedance of the second front bonding layer 30. For example, the acoustic impedance of the first front bonding layer 20 may include those having a range of 12 to 14 MRayL. For example, the first front bonding layer 20 may comprise a borosilicate glass system having an acoustic impedance in the range of 12 to 14 MRayL.

The second front bonding layer 30 may comprise a material that allows ultrasound energy to penetrate the skin tissue as much as possible. In addition, the acoustic impedance of the second front bonding layer 30 may be smaller than the acoustic impedance of the first front bonding layer 20. For example, the acoustic impedance of the second front bonding layer 30 may include those having a range of 3 to 4 MRayL. For example, the second front bonding layer 30 may include an acrylic resin system having an acoustic impedance ranging from 3 to 4 MRayL.

The ultrasound focusing lens 40 can uniformly irradiate ultrasound energy generated in the front portion of the moxibustion therapy ultrasound transducer 100 to the subcutaneous tissue. In addition, the temperature of the subcutaneous tissue can be kept constant, for example, at about 40 캜, without a sudden temperature rise of the subcutaneous tissue.

The number and / or size of the ultrasound focusing lens 40 formed on the second front bonding layer 30 may vary according to the ultrasonic frequency applied to the ultrasonic transducer 100 for moxibustion therapy. In addition, the number and / or size of the ultrasound focusing lens 40 can be changed so that the ultrasound energy can be irradiated to the lower part of the skin area of the moxibustion area. At this time, the ultrasonic frequency may include, for example, 1 to 5 MHz.

Table 1 shows the sizes of the ultrasound focusing lenses according to the ultrasonic frequency.

Ultrasonic frequency (MHz) Piezoelectric element diameter (mm) Ultrasonic focusing lens diameter (mm) Ultrasonic focusing distance (mm) Focal point diameter (mm) Second Front Bonding Layer Thickness (mm) One 30 11 30 10 0.7 3 30 6 30 5.6 0.23 5 30 5 30 4.4 0.14

4 is a view schematically showing the design of the ultrasonic focusing lens according to the present invention.

4A and 4B, FIG. 4A is a diagram showing the configuration of the ultrasonic focusing lens 40 when the piezoelectric element is 30 mm in diameter, the ultrasonic focusing distance is 30 mm, and the ultrasonic frequency is 1 MHz. . At this time, the four ultrasound focusing lenses 40 may be formed on the second front bonding layer 30. The diameter of the ultrasonic focusing lens 40 is 11 mm, the diameter of the focusing point is 10 mm, and the thickness of the second front bonding layer 30 is 0.7 mm.

4 (b) shows the ultrasonic focusing lens 40 when the diameter of the piezoelectric element is 30 mm, the ultrasonic focusing distance is 30 mm, and the ultrasonic frequency is 3 MHz. At this time, nine ultrasonic focusing lenses 40 can be formed. The diameter of the ultrasonic focusing lens 40 is 6 mm, the diameter of the focusing point is 5.6 mm, the thickness of the second front bonding layer 30 is 0.23 mm Can be implemented.

4 (c) shows the ultrasonic focusing lens 40 when the piezoelectric element is 30 mm in diameter, the ultrasonic focusing distance is 30 mm, and the ultrasonic frequency is 5 MHz. At this time, thirteen ultrasonic focusing lenses 40 can be formed, the diameter of the ultrasonic focusing lens 40 is 5 mm, the diameter of the focusing point is 4.4 mm, the thickness of the second front bonding layer 30 is 0.14 mm Can be implemented.

2 is a photograph schematically showing an ultrasonic focusing lens according to embodiments of the present invention.

Referring to FIG. 2, the ultrasound focusing lens 40 may have various shapes. For example, as shown in FIG. 2 (a), it may be formed of a spherical ultrasound focusing lens 40. It may also be formed by a step-like ultrasonic focusing lens 40 as shown in Fig. 2 (b). However, the ultrasound focusing lens of the present invention is not limited thereto, and may be formed in various shapes such that ultrasound energy can be uniformly irradiated to the subcutaneous tissue.

3 is a graph of sound pressure distribution analysis of an ultrasonic focusing lens according to embodiments of the present invention.

3 (a) is a graph showing a sound pressure denominator and temperature analysis when an ultrasonic frequency of 1 MHz is applied to the spherical ultrasound focusing lens having a thickness of? / 4. FIG. 3 (b) is a graph showing sound pressure distribution and temperature analysis when an ultrasonic frequency of 1 MHz is applied to the step-like ultrasonic focusing lens having a thickness of? / 4.

3 (a) and 3 (b), it can be seen that the spherical ultrasound focusing lens has more uniform sound pressure distribution characteristics than the step-like ultrasound focusing lens.

5 is a graph of performance of an ultrasonic focusing lens according to embodiments of the present invention.

5 is a spherical ultrasound focusing lens having a thickness of 3? / 4, and FIG. 5 is a spherical ultrasound focusing lens having a thickness of? / 4. 5 is a step-like ultrasonic focusing lens having a thickness of? / 2, and FIG. 5 is a step-like ultrasonic focusing lens having a thickness of? / 4.

5, a spherical ultrasound focusing lens 1 having a thickness of 3? / 4 is composed of a spherical ultrasound focusing lens 2 having a thickness of? / 4, a stepped It can be seen that the amplitude according to distance is most effective than the ultrasonic focusing lens 3 and the stepped ultrasonic focusing lens 4 having a thickness of? / 4. That is, it can be seen that the spherical ultrasound focusing lens 1 having a thickness of 3? / 4 exhibits the most efficient focusing effect.

In general, moxa moxa is placed directly on the moxibustion area, and there is indirect moxibustion method in which the moxibustion is put on a moxa mugwort on top of the moxibustion area and the indirect moxibustion method in which the moxa is burned and burned.

The direct moxibustion method has a large and rapid therapeutic effect, however, the pain can be severe and scars due to burns on the skin may remain. The indirect moxibustion method has a problem that the moxibustion effect is relatively small and there is no scar due to burn but the moxibustion treatment speed is slow.

In addition, the above methods may cause difficulty in breathing due to smoke generated in the process of sowing mugwort. Especially, there may be problems in respiratory health caused by combustion of other harmful substances contained in mugwort.

However, the above-described problems can be solved by the ultrasonic transducer for moxibustion therapy according to the embodiments of the present invention.

For example, the ultrasonic transducer for moxibustion treatment of the present invention includes a second front bonding layer having at least one piezoelectric element, a first front bonding layer, and an ultrasonic focusing lens, and the ultrasonic wave is uniformly distributed You can investigate. In addition, the temperature of the subcutaneous tissue can be kept constant without a sudden temperature rise of the subcutaneous tissue. In addition, it is possible to solve the inconvenience such as an image of the moxibustion contact portion and difficulty in breathing due to smoke at moxibustion combustion.

In addition, the moxibustion stimulation region can be maintained at a constant temperature, for example, at about 40 ° C, and the moxibustion stimulation time can be controlled by interlocking with an appropriate timing device. In addition, it is possible to minimize the number of management personnel such as burn prevention due to the combustion of the existing moxibustion.

FIG. 6 is a graph showing the results of measuring the skin surface temperature and the skin surface temperature by applying the ultrasonic transducer for moxibustion therapy according to the embodiments of the present invention to the skin of a laboratory rat. Specifically, Fig. 6A is a graph of 20Gain / 1 MHz applied to the skin of experimental rats. FIG. 6B is a graph of 20Gain / 1 MHz measured on the deep surface of the experimental rat. FIG. 6C is a graph of 20Gain / 5 MHz applied to the skin of experimental rats. Referring to FIG. 6, it can be seen that the temperature increase effect of each part over time is maintained, and a constant temperature distribution is maintained at about 40 ° C. for each part.

While the present invention has been described with reference to exemplary embodiments, it is to be understood that the invention is not limited to the disclosed exemplary embodiments, but, on the contrary, is intended to cover various modifications and equivalent arrangements included within the spirit and scope of the invention. Accordingly, the true scope of the present invention should be determined by the technical idea of the appended claims.

10: piezoelectric element
20: first front bonding layer
30: second front bonding layer
40: Ultrasonic focusing lens
50: inner case
60: outer case
70: Signal line
80: Ground wire

Claims (8)

A piezoelectric element;
A first front bonding layer bonded to at least one surface of the piezoelectric element; And
And a second front bonding layer bonded to a surface of the first front bonding layer opposite to a surface bonded to the piezoelectric element,
Wherein at least one ultrasonic focusing lens is formed on the second front bonding layer. The method according to claim 1,
Wherein the acoustic impedance of the first front bonding layer comprises a value larger than the acoustic impedance of the second front bonding layer. 3. The method of claim 2,
Wherein the acoustic impedance of the first front bonding layer comprises a range of 12 to 14 MRayL and the acoustic impedance of the second front bonding layer has a range of 3 to 4 MRayL. The method of claim 3,
Wherein the first front bonding layer comprises a borosilicate glass system and the second front bonding layer comprises an acrylic resin system. The method according to claim 1,
Wherein the piezoelectric element has a piezoelectric constant value of 600 pC / N or more. The method according to claim 1,
Wherein the number and / or size of the lens for ultrasound focusing are different from those formed on the second front bonding layer according to an applied ultrasonic frequency. The method according to claim 6,
Wherein the ultrasonic frequency is in the range of 1 to 5 MHz. The method according to claim 1,
Further comprising a case including the piezoelectric element, the first front bonding layer, and the second front bonding layer.

KR1020140175323A 2014-12-08 2014-12-08 An ultrasonic transducer for moxibustion therapy KR20160069399A (en)

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Cited By (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
KR20180037349A (en) * 2016-10-04 2018-04-12 주식회사 제이시스메디칼 Ultrasound medical apparatus with acoustic lens
KR20180061105A (en) * 2018-05-24 2018-06-07 한국 한의학 연구원 Ultrasonic transducer
KR20180092729A (en) * 2017-02-10 2018-08-20 한국표준과학연구원 An ultrasonic transducer for moxibustion therapy having temperature sensor
KR20200008651A (en) * 2020-01-17 2020-01-28 주식회사 제이시스메디칼 Ultrasound medical apparatus with acoustic lens
WO2020251200A1 (en) * 2019-06-14 2020-12-17 엘지이노텍 주식회사 Mask and skin care device including same

Cited By (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
KR20180037349A (en) * 2016-10-04 2018-04-12 주식회사 제이시스메디칼 Ultrasound medical apparatus with acoustic lens
KR20180092729A (en) * 2017-02-10 2018-08-20 한국표준과학연구원 An ultrasonic transducer for moxibustion therapy having temperature sensor
KR20180061105A (en) * 2018-05-24 2018-06-07 한국 한의학 연구원 Ultrasonic transducer
WO2020251200A1 (en) * 2019-06-14 2020-12-17 엘지이노텍 주식회사 Mask and skin care device including same
KR20200008651A (en) * 2020-01-17 2020-01-28 주식회사 제이시스메디칼 Ultrasound medical apparatus with acoustic lens

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