WO2010034158A1 - 便携式远红外线热灸理疗装置 - Google Patents

便携式远红外线热灸理疗装置 Download PDF

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Publication number
WO2010034158A1
WO2010034158A1 PCT/CN2008/072548 CN2008072548W WO2010034158A1 WO 2010034158 A1 WO2010034158 A1 WO 2010034158A1 CN 2008072548 W CN2008072548 W CN 2008072548W WO 2010034158 A1 WO2010034158 A1 WO 2010034158A1
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WIPO (PCT)
Prior art keywords
power
heat generating
unit
power supply
generating unit
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Ceased
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PCT/CN2008/072548
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English (en)
French (fr)
Inventor
林一峰
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Individual
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Individual
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Application filed by Individual filed Critical Individual
Priority to PCT/CN2008/072548 priority Critical patent/WO2010034158A1/zh
Priority to US13/121,088 priority patent/US20110295349A1/en
Priority to JP2011528158A priority patent/JP5314151B2/ja
Priority to CN200880131307.8A priority patent/CN102164634B/zh
Priority to EP08877030A priority patent/EP2338568A4/en
Publication of WO2010034158A1 publication Critical patent/WO2010034158A1/zh
Anticipated expiration legal-status Critical
Ceased legal-status Critical Current

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Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N5/00—Radiation therapy
    • A61N5/06—Radiation therapy using light
    • A61N5/0613—Apparatus adapted for a specific treatment
    • A61N5/0619—Acupuncture
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N5/00—Radiation therapy
    • A61N5/06—Radiation therapy using light
    • A61N5/0613—Apparatus adapted for a specific treatment
    • A61N5/0616—Skin treatment other than tanning
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N5/00—Radiation therapy
    • A61N5/06—Radiation therapy using light
    • A61N2005/0635—Radiation therapy using light characterised by the body area to be irradiated
    • A61N2005/0643—Applicators, probes irradiating specific body areas in close proximity
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N5/00—Radiation therapy
    • A61N5/06—Radiation therapy using light
    • A61N2005/0658—Radiation therapy using light characterised by the wavelength of light used
    • A61N2005/0659—Radiation therapy using light characterised by the wavelength of light used infrared
    • A61N2005/066—Radiation therapy using light characterised by the wavelength of light used infrared far infrared

Definitions

  • the invention relates to a physiotherapy device, in particular to a portable far infrared thermal moxibustion physiotherapy device. Background technique
  • Physiotherapy is the abbreviation of physical therapy, which is to apply artificial or natural physical factors to the human body to make a favorable response to prevent or treat diseases.
  • Commonly used physical factors include electrical, optical, acoustic, magnetic, temperature, and mechanical forces.
  • thermo therapy devices often require high temperatures to infiltrate the heat generated by the skin from the surface of the skin to the target site, so that the skin will withstand unbearable high temperatures, and the target site often fails to reach the desired temperature. It is easy to burn the skin, but it can't reach the physiotherapy effect. In the end, it can only be half the effort.
  • a far-infrared physiotherapy device without a fever function that is, a passive far-infrared physiotherapy device
  • a passive far-infrared physiotherapy device has appeared on the market.
  • the far-infrared physiotherapy devices do not have the function of inducing far-red emission, the far-infrared emissivity is very low, and the effect of preventing or treating diseases is basically not achieved.
  • the active far-infrared physiotherapy device can utilize thermal energy to excite far-infrared emission, such far-infrared physiotherapy devices consume a large amount of power and must be plugged in, thereby limiting the user's necessity to use it in a fixed position and not to move at will. Summary of the invention
  • a main object of the present invention is to provide a portable far infrared thermal moxibustion physiotherapy apparatus comprising at least one heat generating unit; and a power supply control device connected to the heat generating unit for supplying power thereto and comprising: a charging control circuit connected to the power supply port for receiving electrical energy input by the external power source; a power storage device connected to the charging control circuit for charging; and a power output control unit respectively connecting the charging control circuit and the power storage device
  • the heat generating unit transmits power from the power storage device or power input by the external power source through the charging control circuit to the heat generating unit; and a micro processing unit connected to the power storage device and charging a control circuit and a power output control unit to control whether the external power source supplies power to the power output control unit through the charge control circuit or the power storage device, respectively, according to whether the charge control circuit receives the power input of the external power source Power is supplied to the heat generating unit, and an operation mode of the heat generating unit is controlled by controlling a manner in
  • the power supply control device may further include a temperature sensor disposed adjacent to the heat generating unit to detect a temperature of the heat generating unit, and connected to the micro processing unit to send a signal indicating the detected temperature to the micro processing unit for the micro The processing unit compares the detected temperature with a preset temperature of the heat generating unit stored in the storage unit.
  • the power supply control device may further include an operation mode selecting unit connected to the micro processing unit to select a working mode of the heat generating unit by the user and to issue a corresponding signal to the micro processing unit.
  • the operating mode of the heat generating unit includes a single heating mode and a continuous heating mode, wherein when the micro processing unit receives a signal of the single heating mode from the working mode selecting unit, the micro processing unit instructs the power output
  • the control unit supplies power to the heat generating unit to the preset temperature; when the micro processing unit receives the signal of the continuous heating mode from the working mode selecting unit, the micro processing unit instructs the power output control unit to supply power through the series The period periodically supplies power to the heat generating unit.
  • Each power supply cycle includes: a full power supply phase, wherein the power output control unit supplies power to the heat generating unit without interruption, so that the heat generating unit rapidly heats up to a preset temperature; an intermittent power supply warming phase, wherein the power output The control unit supplies power to the heat generating unit in an intermittent manner in which the power supply time is longer than the power-off time, so that the temperature of the heat generating unit is gradually increased to a preset temperature; the intermittent power supply maintaining phase, wherein the power output control unit has a shorter power supply time than the pause The intermittent mode of the power supply time supplies power to the heat generating unit to maintain the temperature of the heat generating unit; and stops the power supply phase, wherein the power output control unit stops supplying power to the heat generating unit for a certain period of time.
  • the microprocessor unit sets the overall time of the first three phases of the power cycle to 5-60 minutes, and sets the time to stop the power phase to 0-30 minutes.
  • the power control device may include an optimal temperature confirmation unit coupled to the micro processing unit to issue a temperature confirmation signal to the micro processing unit by the user, wherein the temperature confirmation is received by the micro processing unit
  • the current state of the charge control circuit, the power storage device, and the power output control unit is stored in the storage unit to control the target data of the charge control circuit, the power storage device, and the power output control unit as the microprocessor unit .
  • the heat generating unit includes a substrate, a semiconductor heating resistor film coated on the surface of the substrate, and a setting a conductive electrode around the semiconductor heating resistor film and a wire connecting the conductive electrode and the power supply control device to supply power to the semiconductor heating resistor film.
  • the substrate can be made of ceramic, glass or high temperature resistant plastic.
  • the substrate may be made of stainless steel, aluminum alloy or copper, and an insulating layer is provided between the semiconductor heating resistor film and the conductive electrode and the substrate.
  • the heat generating unit may further include a protective member provided on a side of the substrate coated with the semiconductor heat generating resistive film and made of ceramic, glass or high temperature resistant plastic.
  • the surface of the substrate opposite to the semiconductor heat-generating resistive film is coated with a far-infrared strong-emitting material.
  • the far-infrared strong emitting material may be alumina, iron oxide, silicon oxide, titanium oxide, rare earth metal oxide or carbon.
  • a magnet is provided around the periphery of the substrate.
  • the portable far infrared thermal moxibustion physiotherapy apparatus may further include a carrier having at least one of the heat generating units disposed on a surface thereof.
  • the carrier may be a housing, the heat generating unit is disposed on the surface of the housing, and the housing includes two opposite halves to form an internal cavity in which the power supply control device is disposed.
  • the carrier is a housing, and the heat generating unit is opposed to one or both end faces of the housing to form an internal cavity, and the power supply control device is disposed in the internal cavity.
  • the carrier is a drawstring, a silicone adhesive film or a medical tape, and the heat generating unit is attached to a belt, a silicone adhesive film or a medical tape.
  • the number of the heat generating units is two or more and is fixed to a human acupuncture point or a painful position using the carrier.
  • FIG. 1 is a view of a first embodiment of a portable far-infrared hot moxibustion physiotherapy apparatus of the present invention
  • FIG. 2 is a side view of the portable far-infrared hot moxibustion physiotherapy apparatus shown in FIG.
  • Figure 3 is a block diagram showing a first embodiment of a power supply control device for a portable far infrared thermal moxibustion physiotherapy device of the present invention
  • Figure 4 is a block diagram showing a second embodiment of a power supply control device for a portable far infrared heat moxibustion physiotherapy device of the present invention
  • FIG. 5 is a view showing an embodiment of a heat generating unit used in the portable far infrared heat moxibustion physiotherapy apparatus of the present invention
  • Figure 6 is a side view of the heat generating unit shown in Figure 5;
  • Figure 7 is a view of the heat generating unit shown in Figure 5 after removing the protective member
  • Figure 8 is a view showing a modification of the heat-generating unit removing protection member shown in Figure 5;
  • Figure 9 is a view showing another embodiment of a heat generating unit used in the portable far infrared heat moxibustion physiotherapy apparatus of the present invention;
  • Figure 10 is a view showing a second embodiment of the portable far-infrared hot moxibustion physiotherapy apparatus of the present invention
  • Figure 11 is a view showing a third embodiment of the portable far-infrared hot moxibustion physiotherapy apparatus of the present invention
  • Figure 12 is a portable view of Figure 11.
  • Fig. 1 shows a portable far infrared thermal moxibustion physiotherapy apparatus 1 of the present invention comprising a housing 2 and at least one heat generating unit 3 disposed on a surface of the housing.
  • Fig. 2 shows that a heat generating unit 3 is provided on each of two opposite surfaces of the casing 2. However, it is also possible to provide two or more heat generating units 3 on the surface of the casing.
  • the housing 2 can include two opposing halves to form an internal cavity.
  • a power supply control device for supplying power to the heat generating unit 3 may be provided in the internal cavity of the casing, and the power supply control device will be described in detail below with reference to Figs.
  • Fig. 3 is a block diagram showing a first embodiment of a power supply control device for a portable far infrared heat moxibustion physiotherapy apparatus of the present invention.
  • the power supply control device comprises: a micro processing unit (MCU) 6; a charging control circuit 7 connected to the power supply port 5 disposed at a side of the casing 2 to receive electrical energy input by an external power source; and the power storage device 8 connected to the charging device
  • the control circuit 7 is configured to perform charging;
  • the power output control unit 9 respectively connects the charging control circuit 7 and the power storage device 8 to the heat generating unit 3 to transmit the power from the charging control circuit 7 or the power storage device 8 to the heat generating unit 3;
  • a temperature sensor 10 which is disposed adjacent to the heat generating unit 3 and connected to the micro processing unit 6 to detect the temperature of the heat generating unit 3, and sends a signal of the detected temperature to the micro processing unit 6; the storage unit 1 1
  • the data required to perform the control and the corresponding preset temperature value are
  • the power port 5 can include, for example, a USB port to charge the power storage device when plugged into the computer; a car power port to charge the power storage device when plugged into the car cigarette lighter; / or DC port to charge the power storage device when plugged into a normal transformer.
  • the power storage device 8 can be a rechargeable battery pack or other form of rechargeable energy storage device.
  • the micro processing unit 6 is connected to the charge control circuit 7, the power storage device 8, and the power output control unit 9 to control it.
  • the micro processing unit 6 detects that the charging control circuit 7 receives the external input power and charges the power storage device 8, it stops the power storage device 8 from supplying power to the heat generating unit 3 via the power output control unit 9, and directly inputs the power using the external power source. Control via charging control circuit 7 and power output The unit 9 supplies power to the heat generating unit 3. If the micro processing unit 6 detects that the charging control circuit 7 does not receive the external power input, the power storage device 8 is controlled to supply power to the heat generating unit 3 via the power output control unit 9.
  • the power supply control device may further include an operation mode selecting unit 4 disposed on the side of the casing 2, as shown in Fig. 2.
  • the operating mode selection unit 4 is coupled to the microprocessor unit 6 for the user to select the mode of operation of the firing unit 3 and to issue corresponding signals to the microprocessor unit 6. Subsequently, the microprocessor unit 6 controls the power output control unit 9 in accordance with the received operational mode signal to cause the heat generating unit 3 to operate in a corresponding operational mode, e.g., a single thermal mode and a continuous heating mode.
  • the specific operation of the power supply control device shown in Fig. 3 is as follows.
  • the micro processing unit 6 receives the single-heating mode signal from the operating mode selection unit 4, its control power output control unit 9 transmits the power output from the charging control circuit 7 or the power storage device 8 to the heat generating unit 3 to cause heat generation.
  • the temperature of unit 3 rises rapidly.
  • the temperature sensor 10 detects the temperature of the heat generating unit 3 and sends the detected temperature signal to the microprocessor unit 6.
  • the microprocessor unit 6 compares the temperature signal with a preset temperature value previously set in the storage unit 11. When it is determined that the temperature indicated by the temperature signal is lower than the preset temperature, the microprocessor unit 6 instructs the power output control unit 9 to continuously supply power to the heat generating unit 3. When it is determined that the temperature indicated by the temperature signal reaches the preset temperature, the microprocessor unit 6 instructs the power output control unit to stop supplying power to the heat generating unit 3.
  • the micro processing unit 6 When the micro processing unit 6 receives the continuous heating mode signal from the operation mode selecting unit 4, the micro processing unit 6 instructs the power output control unit 9 to periodically supply power to the heat generating unit 3 in a series of power supply cycles.
  • Each cycle consists of four phases: full power supply phase, intermittent power supply warming phase, intermittent power supply sustain phase, and stop power supply phase.
  • the power output control unit 9 supplies power to the heat generating unit 3 without interruption, so that the heat generating unit 3 is rapidly warmed up to a preset temperature.
  • the micro processing unit 6 determines that the temperature of the heat generating unit 3 detected by the temperature sensor 10 is 80-90% of the preset temperature, it controls the power output control unit 9 to enter the second phase, that is, the intermittent power supply warming phase.
  • this full power supply phase is maintained for 1-3 minutes.
  • the power output control unit 9 intermittently supplies power to the heat generating unit 3, wherein the power supply time is longer than the time when the power supply is suspended, so that the temperature of the heat generating unit 3 gradually rises to a preset temperature.
  • the power output control unit 9 can supply power in an intermittent power supply mode in which power is supplied for 1 second every 3-5 seconds of power supply, wherein the heat generating unit 3 is required if necessary. The temperature is raised to the preset temperature as soon as possible, then the power supply is suspended for 5 seconds.
  • the micro processing unit 6 determines that the temperature of the heat generating unit 3 detected by the temperature sensor 10 reaches the preset temperature, it controls the power output control unit 9 to enter the third stage, that is, the intermittent power supply maintaining phase.
  • the power output control unit 9 also intermittently supplies power to the heat generating unit 3.
  • the power supply time is shorter than the time during which the power supply is suspended, so that the temperature of the heat generating unit 3 is maintained for as long as possible, instead of raising its temperature.
  • the power output control unit 9 can supply power in an intermittent power supply mode in which the power supply is temporarily suspended for 3-5 seconds per power supply.
  • the microprocessor unit 6 instructs the power output control unit 9 to enter the fourth phase, that is, to stop the power supply phase, so that the site to be treated is received. Get a break. For example, the first three phases are maintained for 30 minutes, and the power-off phase can last for 0-30 minutes.
  • the microprocessor unit 6 stores the temperature of the heat generating unit 3 and the control data in the storage unit 11 for use in the next cycle, thereby completing a power supply cycle. The next power cycle repeats the previous power cycle from the full power supply phase.
  • the charging control circuit 7 or the power storage device 8 can periodically supply power to the heat generating unit 3 via the power output control unit 9, and intermittently supply power in each cycle, thereby The heating unit 3 is maintained for a longer period of time with less power.
  • the working mode selecting unit 4 can also issue a selection signal to the micro processing unit 6 to cause the micro processing unit 6 to control the power output control unit 9.
  • the selected one or more firing cells 3 are powered so that the selected one or more firing cells 3 operate while the other unselected firing cells 3 do not operate.
  • the plurality of selected firing cells 3 can operate in the same operating mode or in different operating modes.
  • Fig. 4 is a block diagram showing a second embodiment of a power supply control device for the portable far infrared heat moxibustion treatment device of the present invention.
  • This second embodiment is basically the same as the first embodiment except that the second embodiment replaces the temperature sensor 10 in the first embodiment with the optimum temperature confirming unit 12.
  • the optimum temperature confirmation unit 12 is coupled to the microprocessor unit 6 to issue a temperature confirmation signal to the latter.
  • the optimal temperature confirmation unit 12 works in a specific manner, and the user determines to send according to his own perception. Whether the thermal unit 3 has reached its desired temperature. When the user feels that the temperature of the heat generating unit 3 has reached its desired temperature, a temperature confirmation signal is sent to the micro processing unit 6 by the optimum temperature confirming unit 12.
  • the micro processing unit 6 stores the state of the charging control circuit 7 and/or the power storage device 8 and the power supply state of the power generation control unit 9 for the heat generating unit 3 in the storage unit 11 as power supply control target data for later use. In use, control individual components as close as possible to these target data. With the optimum temperature confirmation unit 12, the user can confirm the optimal temperature state of the heat generating unit at any time to meet the needs of different users.
  • the heat generating unit 3 may include a substrate 13 , a semiconductor heating resistor film 16 coated on the surface of the substrate 13 , a conductive electrode 17 disposed around the semiconductor heating resistor film 16 , and a connecting electrode 17 . And the wire 15 of the above power supply control device.
  • the substrate 13 may be made of an insulating material such as ceramic, glass or high temperature resistant plastic. Thereby, the semiconductor heat-generating resistive film 16 and the conductive electrode 17 can be directly disposed on the substrate 13.
  • the substrate 13 may be made of a conductive material such as stainless steel, aluminum alloy, copper or the like. Thus, before the semiconductor heat-generating resistive film 16 and the conductive electrode 17 are disposed on the substrate 13, an insulating layer needs to be coated on the substrate 13.
  • the semiconductor heat-generating resistor film 16 can generate heat and emit far-infrared rays.
  • the far-infrared hot moxibustion treatment can be performed on the corresponding position.
  • the heat generating unit 3 may further include a protective member 14 disposed on a side of the substrate 13 coated with the semiconductor heat-generating resistive film 16.
  • the protective member 14 may be formed of an insulating material such as ceramic, glass or high temperature resistant plastic.
  • the protective member 14 can function as a fixing wire 15 and heat insulation.
  • a far-infrared strong-emitting material such as alumina, iron oxide, silicon oxide, titanium oxide, or rare earth may be coated on the surface of the substrate 13 opposite to the semiconductor heat-generating resistive film 16.
  • Metal oxide or carbon may be coated on the surface of the substrate 13 opposite to the semiconductor heat-generating resistive film 16.
  • the semiconductor heat-generating resistive film 16 may be coated on the substrate 13 in a different shape according to different needs.
  • FIG. 7 shows that the semiconductor heat-generating resistive film 16 is circular
  • FIG. 8 shows the semiconductor heat-generating resistive film 16 It is a rectangle.
  • Fig. 9 shows another embodiment of the heat generating unit of the present invention.
  • the heat generating unit shown in Figure 9 The heat generating unit shown in Figure 9 differs only in that one or more magnets 18, for example, permanent magnets, are provided around the substrate 13 of the heat generating unit of Fig. 9.
  • the far infrared rays emitted by the heat generating unit and the magnetic field generated by the magnet can act together on the site to be treated for physical therapy.
  • the housing 2 can assume an elliptical shape as shown in FIG. However, the housing may also be formed in different shapes.
  • the housing 21 is formed in a circular drum shape, and one end surface or both end surfaces thereof are opposed to the heat generating unit 3 to form a power supply control device.
  • the internal cavity can be provided with the operating mode selection unit 4 and the power supply port 5 on the side of the housing.
  • the portable far-infrared hot moxibustion physiotherapy apparatus of the present invention can be constructed as a massage stone, a sauna stone, a hand warmer, a 3 footer or a warm body for a hot spot.
  • the heat generating unit 3 disposed on the surface of the casing 2 or the heat generating unit that is opposed to the casing 21 is aligned with the corresponding acupuncture point or the painful position, and the far infrared ray heat moxibustion treatment can be performed on the physiotherapy position.
  • the firing unit 3 can also form a separate component, as shown in Figures 11 and 12, or form an external component, as shown in Figures 5-9.
  • the heat generating unit 3 is directly connected via its wire 15 to a power supply, such as the power supply control device described above, and is aligned with the corresponding acupoint or pain position. Therefore, the power supply control device can supply power to the semiconductor heat-generating resistor film 16 of the heat generating unit 3, so that the semiconductor heat-generating resistor film 16 generates heat and emits far-infrared rays outward, and the far-infrared heat-mox moxibustion treatment is performed on the treatment site.
  • the housing 2 can also be designed in different shapes according to ergonomic principles to suit the needs of different parts of the human body.
  • the above-described independent heat generating unit or external heat generating unit may be attached to the band 20 for use.
  • the physiotherapy device of the present invention is constructed as a portable far infrared thermal moxibustion physiotherapy belt 19, as shown in FIG.
  • the heat generating unit 3 is attached to the band 20 by, for example, a Velcro, a mesh cloth or an adhesive.
  • two or more heat generating units 3 may be attached to the band 20 in accordance with the position of the human body acupuncture points, and the heat generating unit 3 is connected to the above-described power supply control device via the wires 15 for power supply by the power supply control device.
  • the heat generating unit or the external heat generating unit may also be attached to a silicon adhesive film, a medical adhesive tape or other material capable of fixing the heat generating unit to the human body, and using a silicon adhesive film, a medical adhesive tape or the like to fix the heat generating unit to the human body.
  • the material is fixed at the acupuncture point or the painful position of the human body.
  • the invention uses a semiconductor heating resistor film as a heat generating component to generate far infrared rays, which can generate strong far infrared rays at a lower temperature, so that the physiotherapy effect is better than ordinary far infrared ray therapy equipment.
  • a semiconductor heating resistor film as a heat generating component to generate far infrared rays, which can generate strong far infrared rays at a lower temperature, so that the physiotherapy effect is better than ordinary far infrared ray therapy equipment.
  • the low-infrared heat-removing physiotherapy device of the present invention uses a semiconductor heating resistor film to generate a far-infrared heat, the power consumption is very small, for example, at 2. 5V ⁇ 3. 6V / 0. 7W ⁇ 0. 8W That is, it can produce about 40 ⁇ 44.
  • the heat generating unit can operate in different working modes, so that the far infrared heat moxibustion physiotherapy device can be operated for a long time under the power supply control device. Therefore, the far-infrared hot moxibustion physiotherapy device of the present invention is convenient to carry around, and is not limited by a fixed power source.

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Description

便携式远红外线热灸理疗装置 技术领域
本发明涉及一种理疗装置， 尤其是一种便携式远红外线热灸理疗装置。 背景技术
理疗是物理治疗的简称， 就是将人工或自然的物理因素作用于人体， 使 之产生有利的反应， 以达到预防或治疗疾病目的。常用人工的物理因素包括 电、 光、 声、 磁、 温度和机械力等。
通常， 人们釆用较多是以温度作为物理因素的理疗装置， 即热敷理疗装 置。然而，传统的热敷理疗装置往往需要很高的温度才能将其产生的热能由 皮肤表层渗透到目的部位，如此皮肤将要承受难以忍受的高温， 而目的部位 却往往无法达到所需要的温度，这样就很容易烫伤皮肤， 而又达不到理疗效 果， 最终只能是事倍功半。
目前， 市场上已经出现了一种无发热功能的远红外线理疗装置， 即被动 式远红外线理疗装置。然而， 由于此类远红外线理疗装置没有热能激发远红 外线发射的功能，故其远红外线发射率非常低，基本达不到预防或治疗疾病 的效果。
虽然主动式远红外线理疗装置可以利用热能激发远红外线发射， 但是此 类远红外线理疗装置耗电大，故必须插电使用，从而限制了使用者必须要在 固定位置使用而不得随意移动。 发明内容
针对上述问题， 本发明的主要目的在于提供一种便携式远红外线热灸理 疗装置， 其包括至少一个发热单元； 和供电控制装置， 该供电控制装置连接 于该发热单元以对其进行供电并包括： 充电控制电路， 其连接于供电端口， 以接收外部电源输入的电能； 蓄电装置， 其连接于充电控制电路， 以进行充 电； 电力输出控制单元， 其分别将该充电控制电路和蓄电装置连接于该发热 单元， 以将来自该蓄电装置的电能或该外部电源通过该充电控制电路输入的 电能传输至该发热单元； 以及微处理单元， 其分别连接于该蓄电装置、 充电 控制电路和电力输出控制单元， 以根据该充电控制电路是否接收该外部电源 的电能输入来控制分别由该外部电源通过该充电控制电路或由该蓄电装置向 该电力输出控制单元提供电能， 以向该发热单元供电， 并且通过控制该电力 输出控制单元向该发热单元供电的方式来控制该发热单元的工作模式。
该供电控制装置还可以包括温度传感器， 其靠近该发热单元设置以检测 该发热单元的温度， 并且连接于该微处理单元以向该微处理单元发出表示所 检测到温度的信号， 以供该微处理单元将检测到的温度与储存于存储单元中 的发热单元预设温度进行比较。 另外， 该供电控制装置还可以包括工作模式 选择单元， 其连接于该微处理单元， 以由使用者通过其选择该发热单元的工 作模式并向微处理单元发出相应信号。
优选地， 该发热单元的工作模式包括单次发热模式和持续发热模式， 其 中， 当该微处理单元从该工作模式选择单元接收到单次发热模式的信号时， 该微处理单元指令该电力输出控制单元向该发热单元供电至该发热单元达到 预设温度； 当该微处理单元从该工作模式选择单元接收到持续发热模式的信 号时， 该微处理单元指令该电力输出控制单元以一系列供电周期向该发热单 元周期性供电。 每一供电周期依次包括： 全功率供电阶段， 其中该电力输出 控制单元不间断地向该发热单元供电， 以使该发热单元快速升温至接近预设 温度； 间歇式供电升温阶段， 其中该电力输出控制单元以供电时间长于暂停 供电时间的间歇方式向该发热单元供电， 以使该发热单元的温度逐步上升至 预设温度； 间歇式供电维持阶段， 其中该电力输出控制单元以供电时间短于 暂停供电时间的间歇方式向该发热单元供电， 以维持该发热单元的温度； 和 停止供电阶段， 其中该电力输出控制单元停止向该发热单元供电一段特定时 间。
优选地，该微处理单元将供电周期的前三个阶段的总体时间设定为 5-60 分钟， 而将停止供电阶段的时间设定为 0-30分钟。
或者， 该供电控制装置可以包括最佳温度确认单元， 其连接于该微处理 单元， 以由使用者通过其向该微处理单元发出温度确认信号， 其中当供该微 处理单元接收到该温度确认信号时， 则将该充电控制电路、 蓄电装置和电力 输出控制单元的当前状态储存于存储单元中， 以作为该微处理单元控制该充 电控制电路、 蓄电装置和电力输出控制单元的目标数据。
该发热单元包括基板、 涂覆在该基板表面的半导体发热电阻薄膜、 设置 在该半导体发热电阻薄膜周边的导电极以及连接该导电极和该供电控制装置 以向该半导体发热电阻薄膜供电的导线。 该基板可以由陶瓷、 玻璃或耐高温 塑料制成。 或者， 该基板可以由不锈钢、 铝合金或铜制成， 并且在半导体发 热电阻薄膜和导电极与基板之间设置有绝缘层。
该发热单元还可以包括保护部件， 该保护部件设置在该基板涂覆有该半 导体发热电阻薄膜的一侧并且由陶瓷、 玻璃或耐高温塑料制成。
优选地， 该基板的与半导体发热电阻薄膜相对的表面上涂覆有远红外线 强发射材料。 该远红外线强发射材料可以为氧化铝、 氧化铁、 氧化硅、 氧化 钛、 稀土金属氧化物或碳。
另外， 该基板周边设置有磁体。
该便携式远红外线热灸理疗装置还可以包括载体， 其表面设置至少一个 该发热单元。 该载体可以为壳体， 发热单元设置在壳体表面， 并且壳体包括 两个相对合的半部， 以形成内部空腔， 供电控制装置设置于该内部空腔中。 或者， 该载体为壳体， 发热单元与该壳体的一个或两个端面相对合， 以形成 内部空腔， 供电控制装置设置于该内部空腔中。 抑或， 该载体为束带、 硅粘 胶片或医学胶布， 发热单元附着于在束带、 硅粘胶片或医学胶布上。 该发热 单元的数量为两个或更多并使用该载体固定于人体穴道位置或瘀痛位置上。 附图说明
下面参照附图详细描述本发明， 其中：
图 1是本发明便携式远红外线热灸理疗装置第一实施方式的视图； 图 2是图 1所示便携式远红外线热灸理疗装置的侧视图；
图 3是本发明便携式远红外线热灸理疗装置的供电控制装置第一实施方 式的方块图；
图 4是本发明便携式远红外线热灸理疗装置的供电控制装置第二实施方 式的方块图；
图 5是本发明便携式远红外线热灸理疗装置中使用的发热单元实施方式 的视图；
图 6是图 5所示发热单元的侧视图；
图 7是图 5所示发热单元去除保护部件后的视图；
图 8是图 5所示发热单元去除保护部件的变形形式的视图； 图 9是本发明便携式远红外线热灸理疗装置中使用的发热单元的另一实 施方式的视图；
图 1 0是本发明便携式远红外线热灸理疗装置第二实施方式的视图； 图 1 1是本发明便携式远红外线热灸理疗装置第三实施方式的视图；以及 图 12是图 1 1所示便携式远红外线热灸理疗装置的侧视图。 具体实施方式
图 1示出了本发明的便携式远红外线热灸理疗装置 1 , 其包括壳体 2和 至少一个设置在壳体表面的发热单元 3。 图 2示出在壳体 2的两个相对的表 面各设置有一个发热单元 3。 但是， 也可以在壳体的表面上设置两个以上的 发热单元 3。
如图 2所示， 该壳体 2可以包括两个相对合的半部， 以形成内部空腔。 该壳体的内部空腔中可以设置用于以向发热单元 3供电的供电控制装置， 下 文中将参照图 3和图 4对该供电控制装置进行详细说明。
图 3示出了本发明便携式远红外线热灸理疗装置的供电控制装置第一实 施方式的方块图。 该供电控制装置包括： 微处理单元 (MCU) 6 ; 充电控制电路 7 , 其连接于设置在壳体 2侧面的供电端口 5 , 以接收外部电源输入的电能； 蓄电装置 8 , 其连接于充电控制电路 7 , 以进行充电； 电力输出控制单元 9 , 其分别将充电控制电路 7和蓄电装置 8连接于发热单元 3 , 以将来自充电控 制电路 7或蓄电装置 8的电能传输至发热单元 3; 温度传感器 1 0 , 其靠近发 热单元 3设置并连接于微处理单元 6 , 以检测发热单元 3的温度， 并向微处 理单元 6发出所检测到的温度的信号； 存储单元 1 1 , 用于存储执行控制所需 的数据以及相应的预设温度值。
该供电端口 5可以包括， 例如， USB端口， 以在插接到计算机上时对蓄 电装置进行充电； 汽车电源端口， 以在插接到汽车点烟器上时对蓄电装置进 行充电； 和 /或 DC端口， 以在插接到普通变压器上时对蓄电装置进行充电。
该蓄电装置 8可以是充电电池组或者其他形式充电蓄能装置。 该微处理 单元 6连接于充电控制电路 7、蓄电装置 8和电力输出控制单元 9 , 以对其进 行控制。 当微处理单元 6检测到充电控制电路 7接受外部输入电能并对蓄电 装置 8进行充电时， 其停止蓄电装置 8经由电力输出控制单元 9向发热单元 3供电， 而直接利用外部电源输入电能经由充电控制电路 7和电力输出控制 单元 9向发热单元 3供电。 如果微处理单元 6检测到充电控制电路 7并未接 收外部电能输入， 则控制蓄电装置 8经由电力输出控制单元 9向发热单元 3 供电。
该供电控制装置还可以包括设置在壳体 2侧面的工作模式选择单元 4 , 如图 2所示。 该工作模式选择单元 4连接于微处理单元 6 , 以由使用者通过 其选择发热单元 3的工作模式并向微处理单元 6发出相应信号。 随后， 该微 处理单元 6根据接收到的工作模式信号对电力输出控制单元 9进行控制， 以 使发热单元 3在相应工作模式，例如，单次发热模式和持续发热模式下工作。
图 3所示的供电控制装置的具体工作方式如下。 当微处理单元 6接收到 工作模式选择单元 4发出的单次发热模式信号时， 其控制电力输出控制单元 9将充电控制电路 7或蓄电装置 8输出的电能传输至发热单元 3 ,以使发热单 元 3的温度快速上升。 同时， 温度传感器 10检测发热单元 3的温度， 并向微 处理单元 6发出所检测到的温度信号。 微处理单元 6将该温度信号与预先设 定于存储单元 11中的预设温度值进行比较。当确定温度信号所表示的温度低 于预设温度时， 微处理单元 6指令电力输出控制单元 9持续向发热单元 3供 电。 当确定温度信号所表示的温度达到预设温度时， 微处理单元 6指令电力 输出控制单元停止向发热单元 3供电。
当微处理单元 6接收到工作模式选择单元 4发出的持续发热模式信号时， 微处理单元 6指令电力输出控制单元 9以一系列供电周期向发热单元 3周期 性地供电。 每一周期包括依次四个阶段： 全功率供电阶段、 间歇式供电升温 阶段、 间歇式供电维持阶段、 停止供电阶段。
在全功率供电阶段， 电力输出控制单元 9不间断地向发热单元 3供电， 以使发热单元 3快速升温至接近预设温度。 例如， 当微处理单元 6确定温度 传感器 10检测到的发热单元 3的温度为预设温度的 80-90%时， 其控制电力 输出控制单元 9进入第二阶段， 即间歇式供电升温阶段。 通常， 该全功率供 电阶段维持 1-3分钟。
在间歇式供电升温阶段，电力输出控制单元 9向发热单元 3间歇式供电， 其中供电时间比暂停供电的时间长， 以使发热单元 3的温度逐步上升至预设 温度。例如，根据蓄电装置 8的状态和 /或所需的升温斜率， 该电力输出控制 单元 9可以按照每供电 3-5秒暂停供电 1秒的间歇供电方式进行供电， 其中 如果需要将发热单元 3的温度尽快提升至预设温度， 则每供电 5秒暂停供电 1秒； 而如果需要发热单元 3的温度緩慢上升至预设温度， 则可以每供电 3 秒暂停供电 1秒。 但是， 也可以根据实际情况和需要设定不同的供电和暂停 供电时间比例。当微处理单元 6确定温度传感器 10检测到的发热单元 3的温 度达到预设温度时， 其控制电力输出控制单元 9进入第三阶段， 即间歇式供 电维持阶段。
在间歇式供电维持阶段， 电力输出控制单元 9同样向发热单元 3间歇式 供电。 但是， 在该阶段， 供电时间比暂停供电的时间短， 以尽可能长时间地 维持发热单元 3的温度， 而并非提升其温度。 例如， 根据蓄电装置 8的状态 和 /或所需维持温度时间长短，该电力输出控制单元 9可以按照每供电 1秒暂 停供电 3-5秒的间歇供电方式进行供电。 然而， 也可以根据实际情况和需要 设定不同的供电和暂停供电时间比例。
在将各周期内的前三个阶段维持预定的时间 （例如， 5-60分钟）之后， 微处理单元 6指令电力输出控制单元 9进入第四阶段， 即停止供电阶段， 以 使受理疗的部位得到休息。例如， 前三个阶段维持时间为 30分钟， 而该停止 供电阶段可以持续 0-30分钟。在该阶段，微处理单元 6将发热单元 3的温度 以及控制数据储存于存储单元 11中， 以供下一周期使用，从而， 完成一个供 电周期。 下一供电周期从全功率供电阶段开始重复上一供电周期。 由此， 在 微处理单元 6的控制下， 充电控制电路 7或蓄电装置 8可以经由电力输出控 制单元 9对发热单元 3进行周期性供电，并且在每一周期内进行间歇性供电， 从而可以以较少电能维持发热单元 3较长时间的工作。
另外，当该便携式远红外线热灸理疗装置 1包括多于一个发热单元 3时， 该工作模式选择单元 4还可以向微处理单元 6发出选择信号， 以使微处理单 元 6控制电力输出控制单元 9向被选择的一个或多个发热单元 3供电， 从而 使该被选择的一个或多个发热单元 3工作， 而其他未被选择的发热单元 3不 工作。 被选择的多个发热单元 3可以按照相同的工作模式工作， 或者按照不 同的工作模式工作。
图 4示出了本发明便携式远红外线热灸理疗装置的供电控制装置第二实 施方式的方块图。 该第二实施方式与第一实施方式基本相同， 不同之处仅在 于第二实施方式以最佳温度确认单元 12 代替了第一实施方式中的温度传感 器 10。该最佳温度确认单元 12连接于微处理单元 6 , 以向后者发出温度确认 信号。该最佳温度确认单元 12具体工作方式为，使用者根据自身感知确定发 热单元 3是否已经达到自己希望的温度。 当使用者感受到发热单元 3的温度 达到了其所希望的温度，则通过最佳温度确认单元 12向微处理单元 6发出温 度确认信号。此时，微处理单元 6即将充电控制电路 7和 /或蓄电装置 8的状 态以及电力输出控制单元 9对发热单元 3的供电状态储存于存储单元 11中， 作为供电控制目标数据， 以供以后使用中控制各个部件尽可能趋近这些目标 数据。 利用该最佳温度确认单元 12 , 使用者可以随时对其感受到的发热单元 最佳温度状态进行确认， 以满足不同使用者的需要。
如图 5-7所示， 该发热单元 3可以包括基板 1 3、 涂覆在基板 1 3表面的 半导体发热电阻薄膜 16、 设置在该半导体发热电阻薄膜 16周边的导电极 17 以及连接导电极 17和上述供电控制装置的导线 15。该基板 1 3可以由绝缘材 料制成， 例如， 陶瓷、 玻璃或耐高温塑料等。 从而， 半导体发热电阻薄膜 16 和导电极 17就可直接设置在该基板 1 3上。或者，该基板 1 3也可以由导电材 料制成， 例如， 不锈钢、 铝合金、 铜等。 由此， 在将半导体发热电阻薄膜 16 和导电极 17设置在基板 1 3上之前， 需要在基板 1 3上涂覆一层绝缘层。
在工作状态下， 由于供电电源， 例如上述供电控制装置， 通过导线 15 向半导体发热电阻薄膜 16供电， 半导体发热电阻薄膜 16就可以发热并向外 发出远红外线。 将该发热单元 3对准相应的穴位或者瘀痛位置， 即可对该相 应位置进行远红外线热灸理疗。
为了保护半导体发热电阻薄膜 16和导电极 17 , 该发热单元 3还可以包 括保护部件 14，该保护部件设置在基板 13涂覆有半导体发热电阻薄膜 16的 一侧。 保护部件 14可以由绝缘材料形成， 例如， 陶瓷、 玻璃或耐高温塑料。 同时， 该保护部件 14可以起到固定导线 15以及隔热的作用。 在将发热单元 3设置在壳体 2上时， 可以使基板 1 3面向外侧， 以便在使用时直接面对待理 疗的对象。
为了提高发热单元 3的远红外线发射率，可以在基板 1 3的与半导体发热 电阻薄膜 16相对的表面上涂覆远红外线强发射材料，例如，氧化铝、氧化铁、 氧化硅、 氧化钛、 稀土金属氧化物或者碳等。
另外，根据不同的需要，可以使半导体发热电阻薄膜 16以不同的形状涂 覆在基板 1 3上， 例如， 图 7示出半导体发热电阻薄膜 16呈圓形， 图 8示出 半导体发热电阻薄膜 16呈矩形。
图 9示出了本发明的发热单元的另一实施方式。 图 9所示的发热单元与 图 5所示的发热单元的不同之处仅在于，在图 9的发热单元的基板 1 3周边设 置有一个或多个磁体 18 , 例如， 永久磁铁。 从而， 发热单元发出的远红外线 和磁体发出的磁力场可以共同作用于待理疗的部位， 以进行理疗。
该壳体 2可以呈现椭圓形， 如图 1所示。 但是， 壳体也可以形成不同的 形状， 例如， 如图 11和 12所示， 壳体 21形成为圓鼓形， 其一个端面或者两 个端面与发热单元 3相对合， 以形成容纳供电控制装置的内部空腔， 而在壳 体的侧面同样可以设置工作模式选择单元 4和供电端口 5。 由此， 本发明的 便携式远红外线热灸理疗装置即可构造成用于穴道热敷的按摩石、 桑拿石、 暖手器、 3爰脚器或暖身器。 在使用时， 将设置在该壳体 2表面的发热单元 3 或者与壳体 21对合的发热单元对准相应的穴位或者瘀痛位置，即可对待理疗 位置进行远红外线热灸理疗。
但是， 发热单元 3也可形成独立元件， 如图 11和 12所示， 或者形成外 接式元件， 如图 5-9所示。在使用时， 该发热单元 3直接通过其导线 15连接 于供电电源， 例如上述供电控制装置， 并对准相应的穴位或者瘀痛位置。 从 而，该供电控制装置即可向该发热单元 3的半导体发热电阻薄膜 16供电， 以 使半导体发热电阻薄膜 16发热并向外发出远红外线，而对待理疗位置进行远 红外线热灸理疗。
另外， 该壳体 2也可以根据人体工程学原理设计成不同外形， 以适应人 体不同部位的需要。 例如， 为了满足将发热单元 3定位于大尺寸躯干或部位 的要求， 也可以将上述独立发热单元或外接式发热单元附着于束带 20 上使 用。 从而， 本发明的理疗装置就构造成了便携式远红外线热灸理疗带 19 , 如 图 10所示。 该发热单元 3通过， 例如， 魔术贴、 网状布或粘结剂等， 附着于 束带 20上。特别是， 两个或更多发热单元 3可以按照人体穴道的位置而附着 于束带 20上， 而发热单元 3通过导线 15连接于上述供电控制装置， 以由供 电控制装置进行供电。 在使用时， 仅需使发热单元 3面对待理疗的部位， 并 利用束带 20 进行固定。 该发热单元或外接式发热单元也可以附着于硅粘胶 片、 医学胶布或其它可将发热单元固定在人体的材料， 并利用硅粘胶片、 医 学胶布或其它可将发热单元固定在人体的材料固定于人体穴道位置或瘀痛位 置上。
本发明釆用半导体发热电阻薄膜作为发热部件来产生远红外线， 其可在 较低温度下产生较强的远红外线， 故其理疗效果更优于普通远红外线理疗装 置。 另外， 由于本发明的远红外线热灸理疗装置釆用半导体发热电阻薄膜进 行发热产生远红外线， 其耗电量非常小， 例如， 在 2. 5V ~ 3. 6V/0. 7W ~ 0. 8W 下即可以产生约 40 ~ 44。 C的适当温度， 并且在供电控制装置的控制下， 发 热单元可以在不同工作模式下工作， 从而， 该远红外线热灸理疗装置可以在 供电控制装置下进行较长时间工作。 因此， 本发明的远红外线热灸理疗装置 便于随身携带使用， 而不受固定电源的限制。
尽管参照优选的实施例描述了本发明， 但本发明并不限于此， 本领域的 普通技术人员在不脱离本发明的精神和范围的前提下， 可以对本发明进行各 种改进和变形。

Claims

权利要求书
1. 一种便携式远红外线热灸理疗装置， 包括：
至少一个发热单元； 以及
供电控制装置， 其连接于该发热单元以对其进行供电， 该供电控制装置 包括：
充电控制电路， 其连接于供电端口， 以接收外部电源输入的电能； 蓄电装置， 其连接于该充电控制电路， 以进行充电；
电力输出控制单元， 其分别将该充电控制电路和蓄电装置连接于该 发热单元， 以将来自该蓄电装置的电能或该外部电源通过该充电控制电路输 入的电能传输至该发热单元； 以及
微处理单元， 其分别连接于该蓄电装置、 充电控制电路和电力输出 控制单元， 以根据该充电控制电路是否接收该外部电源的电能输入来控制分 别由该外部电源通过该充电控制电路或由该蓄电装置向该电力输出控制单元 提供电能， 以向该发热单元供电， 并且通过控制该电力输出控制单元向该发 热单元供电的方式来控制该发热单元的工作模式。
2. 如权利要求 1所述的便携式远红外线热灸理疗装置，其中该供电控制 装置还包括温度传感器， 其靠近该发热单元设置以检测该发热单元的温度， 并且连接于该微处理单元以向该微处理单元发出表示所检测到温度的信号， 以供该微处理单元将所述检测到的温度与储存于存储单元中的发热单元预设 温度进行比较。
3. 如权利要求 2所述的便携式远红外线热灸理疗装置，其中该供电控制 装置还包括工作模式选择单元， 其连接于该微处理单元， 以由使用者通过其 选择该发热单元的工作模式并向微处理单元发出相应信号。
4. 如权利要求 3所述的便携式远红外线热灸理疗装置，其中该发热单元 的工作模式包括单次发热模式和持续发热模式， 其中， 当该微处理单元从该 工作模式选择单元接收到单次发热模式的信号时， 该微处理单元指令该电力 输出控制单元向该发热单元供电至该发热单元达到所述预设温度； 当该微处 理单元从该工作模式选择单元接收到持续发热模式的信号时， 该微处理单元 指令该电力输出控制单元以一系列供电周期向该发热单元周期性供电。
5. 如权利要求 4所述的便携式远红外线热灸理疗装置，其中每一所述供 电周期依次包括： 全功率供电阶段， 其中该电力输出控制单元不间断地向该 发热单元供电， 以使该发热单元快速升温至接近所述预设温度； 间歇式供电 升温阶段， 其中该电力输出控制单元以供电时间长于暂停供电时间的间歇方 式向该发热单元供电， 以使该发热单元的温度逐步上升至所述预设温度； 间 歇式供电维持阶段， 其中该电力输出控制单元以供电时间短于暂停供电时间 的间歇方式向该发热单元供电，以维持该发热单元的温度；和停止供电阶段， 其中该电力输出控制单元停止向该发热单元供电一段特定时间。
6. 如权利要求 5所述的便携式远红外线热灸理疗装置，其中该微处理单 元将所述供电周期的前三个阶段的总体时间设定为 5-60分钟，而将所述停止 供电阶段的时间设定为 0-30分钟。
7. 如权利要求 1所述的便携式远红外线热灸理疗装置，其中该供电控制 装置还包括最佳温度确认单元， 其连接于该微处理单元， 以由使用者通过其 向该微处理单元发出温度确认信号， 其中当供该微处理单元接收到该温度确 认信号时， 则将该充电控制电路、 蓄电装置和电力输出控制单元的当前状态 储存于存储单元中， 以作为该微处理单元控制该充电控制电路、 蓄电装置和 电力输出控制单元的目标数据。
8. 如权利要求 1所述的便携式远红外线热灸理疗装置，其中所述发热单 元包括基板、 涂覆在该基板表面的半导体发热电阻薄膜、 设置在该半导体发 热电阻薄膜周边的导电极以及连接该导电极和该供电控制装置以向该半导体 发热电阻薄膜供电的导线。
9. 如权利要求 8所述的便携式远红外线热灸理疗装置，其中所述基板由 陶瓷、 玻璃或耐高温塑料制成。
10. 如权利要求 8所述的便携式远红外线热灸理疗装置， 其中所述基板 由不锈钢、 铝合金或铜制成， 并且在所述半导体发热电阻薄膜和导电极与所 述基板之间设置有绝缘层。
11. 如权利要求 8所述的便携式远红外线热灸理疗装置， 其中所述发热 单元还包括保护部件， 该保护部件设置在该基板涂覆有该半导体发热电阻薄 膜的一侧并且由陶瓷、 玻璃或耐高温塑料制成。
12. 如权利要求 8所述的便携式远红外线热灸理疗装置， 其中在所述基 板的与所述半导体发热电阻薄膜相对的表面上涂覆有远红外线强发射材料。
1 3. 如权利要求 12所述的便携式远红外线热灸理疗装置，其中所述远红 外线强发射材料为氧化铝、 氧化铁、 氧化硅、 氧化钛、稀土金属氧化物或碳。
14. 如权利要求 8所述的便携式远红外线热灸理疗装置， 其中所述基板 周边设置有磁体。
15. 如权利要求 8-14中任一项所述的便携式远红外线热灸理疗装置，还 包括载体， 其表面设置至少一个所述发热单元。
16. 如权利要求 15所述的便携式远红外线热灸理疗装置，其中所述载体 为壳体， 所述发热单元设置在壳体表面， 并且所述壳体包括两个相对合的半 部， 以形成内部空腔， 所述供电控制装置设置于该内部空腔中。
17. 如权利要求 15所述的便携式远红外线热灸理疗装置，其中所述载体 为壳体，所述发热单元与该壳体的一个或两个端面相对合，以形成内部空腔， 所述供电控制装置设置于该内部空腔中。
18. 如权利要求 15所述的便携式远红外线热灸理疗装置，其中所述载体 为束带、 硅粘胶片或医学胶布， 所述发热单元附着于在所述束带、 硅粘胶片 或医学胶布上。
19. 如权利要求 18所述的便携式远红外线热灸理疗装置，其中所述发热 单元的数量为两个或更多并使用所述载体固定于人体穴道位置或瘀痛位置 上。
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