WO2006054359A1 - 無呼吸防止刺激装置 - Google Patents
無呼吸防止刺激装置 Download PDFInfo
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- WO2006054359A1 WO2006054359A1 PCT/JP2004/017337 JP2004017337W WO2006054359A1 WO 2006054359 A1 WO2006054359 A1 WO 2006054359A1 JP 2004017337 W JP2004017337 W JP 2004017337W WO 2006054359 A1 WO2006054359 A1 WO 2006054359A1
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- stimulation
- signal
- electric pulse
- output
- time width
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Classifications
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
- A61N1/00—Electrotherapy; Circuits therefor
- A61N1/18—Applying electric currents by contact electrodes
- A61N1/32—Applying electric currents by contact electrodes alternating or intermittent currents
- A61N1/36—Applying electric currents by contact electrodes alternating or intermittent currents for stimulation
- A61N1/3601—Applying electric currents by contact electrodes alternating or intermittent currents for stimulation of respiratory organs
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
- A61N1/00—Electrotherapy; Circuits therefor
- A61N1/18—Applying electric currents by contact electrodes
- A61N1/32—Applying electric currents by contact electrodes alternating or intermittent currents
- A61N1/36—Applying electric currents by contact electrodes alternating or intermittent currents for stimulation
- A61N1/36014—External stimulators, e.g. with patch electrodes
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
- A61N1/00—Electrotherapy; Circuits therefor
- A61N1/18—Applying electric currents by contact electrodes
- A61N1/32—Applying electric currents by contact electrodes alternating or intermittent currents
- A61N1/36—Applying electric currents by contact electrodes alternating or intermittent currents for stimulation
- A61N1/36014—External stimulators, e.g. with patch electrodes
- A61N1/3603—Control systems
- A61N1/36034—Control systems specified by the stimulation parameters
Definitions
- the present invention relates to an apnea preventing stimulation device that prevents the occurrence of a disorder due to an abnormality in respiratory regulation during sleep.
- Sleep apnea syndrome can be divided into a central type due to respiratory central abnormality, an obstructive type due to obstruction of the upper airway, and a mixed type in which the both are mixed.
- Mount the mouthpiece in the patient's mouth fix the mandible in the anterior position, open the upper airway, or wear a plastic nasal mask at bedtime, and connect it with the nasal cavity mask and a hose.
- Pumping device power A treatment method of pumping air to widen the obstructed upper airway is conventionally known. However, in the former method, the mouthpiece can not breathe the mouth, so it can not be used when the passage of the nose is bad. Also, in the latter method, it is necessary to attach a nasal mask that sends air to the face, which may cause discomfort when sleeping.
- Patent Document 1 when the respiratory state of the treating person is detected by a respiratory detection means such as a thermistor, and this respiratory detection means determines that there is no apnea,
- the frequency is 40-150 Hz
- the wave height is on the tongue tongue muscle, which is one of the open muscles of the upper respiratory tract
- Anti-apnea stimulators have been proposed that provide stimulation signals with electrical pulses with a value of 150 volts and a rise time constant of 0.2 seconds or more to recover the upper airway obstruction.
- the apnea-preventing stimulation device configured as described above provides stimulation signals to the inguinal muscles instead of air pressure, there is no need to wear a nasal mask that covers the face, and it is possible to prevent nasal congestion or not. Regardless, there is an advantage that the upper airway obstruction can be quickly avoided.
- Patent Document 1 Patent 2794196
- the present invention provides an apnea preventing stimulation device that can effectively provide a stimulation signal to the buttocks of a therapist without disturbing the sleep of the patient as much as possible without monitoring the respiratory condition. Its purpose is to provide.
- a conductor is placed on the buttocks of a treatment subject, and an electric pulse is supplied from the conductions to the buttocks of the treatment subject to provide stimulation.
- stimulation generation means for outputting to the conductor a stimulation signal which repeats for a fixed time a conduction period in which an electric pulse group consisting of the plurality of electric pulses is generated and a rest period in which the electric pulse group does not occur. I hate it.
- a first operation means for varying the amplitude of the electrical pulse.
- a second operation means for varying the power supply period.
- a third operation means is provided for varying the idle period.
- a fourth operation hand starting output of the stimulation signal.
- a fifth operation means for stopping the output of the stimulation signal.
- the stimulation generating means is a stimulation signal in which the amplitude of the electrical pulse is gradually increased from the start of the output of the stimulation signal until the first time width elapses. Are output.
- sixth operation means for changing the first time width is provided.
- the stimulation generating means is a stimulation in which a time width of a plurality of electric pulses constituting the electric pulse group is varied during an output period of the electric pulse group. It is characterized by outputting a signal.
- the stimulus generation means alternately generates positive and negative electric pulse groups having a second time width in the energizing period, and starts up from rising of the electric pulse group.
- the time width of each electrical pulse is gradually increased until half of the second time width elapses, and then the time width of each electrical pulse is gradually narrowed as the falling of the electrical pulse group is approached. It is characterized by outputting a stimulation signal.
- the stimulation generation means is configured to change the density of a plurality of electric pulses constituting the electric pulse group during an output period of the electric pulse group. It is characterized by being an output.
- the stimulus generation means generates the electric pulse group having a second time width alternately in the positive and negative periods in the energizing period, and starts from the rising of the electric pulse group.
- the electric pulse density gradually increases until half of the second time width elapses, and then the stimulation signal is output in which the electric pulse density gradually decreases as the electric pulse group approaches falling. It is characterized by being.
- the conductor includes a pair of electrodes to which the stimulation signal is applied, and an adhesive sheet that holds the electrodes and is removable from the buttocks of the therapist. It consists of parts.
- the sheet member arranges the electrodes so that the pair of electrodes are juxtaposed in the front-rear direction of the buttocks of the therapist! Ru.
- a stimulation signal that repeats an energizing period generated by an electric pulse group, an electric pulse group does not occur, and a resting period via a conductor and a stimulation generator means a conductor's buttocks. Because it is given effectively, upper airway obstruction can be quickly avoided without having to monitor respiratory status. In addition, since the buttocks of the therapist who is unrelated to the presence or absence of the therapist's breathing is given a stimulation signal that repeats the energizing period and the rest period of the electric pulse group, the therapist is less likely to notice the stimulation signal. You can get enough sleep. Therefore, it is possible to effectively provide a stimulation signal to the buttocks of the therapist without disturbing the patient's sleep as much as possible without monitoring the respiratory condition.
- the amplitude of the electric pulse generated during the energization period can be varied by the first operation means. Therefore, it is possible to give an electrical pulse of the optimum amplitude to any therapist.
- the energization period in which the electric pulses are generated can be arbitrarily changed by the second operation means. Therefore, it is possible to give a stimulus signal with an optimal energizing period to any therapist.
- the pause period during which the electric noise group does not occur can be arbitrarily changed by the third operation means. Therefore, it is possible to give a stimulus signal with an optimal rest period to any therapist.
- a force stimulation signal at that time can be output to the conductor.
- the treatment can be temporarily discontinued by stopping the output of the stimulation signal by operating the fifth operation means.
- the stimulation signal in which the amplitude of the electric pulse becomes smaller.
- the amplitude of the electrical pulse gradually increases as the patient falls into the sleep state, it is possible to give the therapist a stimulus signal capable of reliably avoiding the apnea state when sleeping.
- the sixth operation means uses the first time. If the width can be varied, it is possible to give a stimulus signal that reliably avoids an apnea condition when going to bed to any therapist.
- the stimulus generation means arbitrarily changes the time width of each of the electric pulses that make up the electric pulse group, the low frequency wave into the therapist according to the increase or decrease of the time width of the electric pulse.
- the shape is preferred and can be distorted into states.
- the stimulation generation means outputs a stimulation signal
- repetition of an electrical pulse group including a plurality of high frequency signal components (electric pulses) is given from the lead as a stimulation signal to the therapist.
- the waveform of the electrical pulse group is distorted, and the stimulation signal becomes a waveform approximating a low frequency sine wave. Therefore, it is possible to effectively avoid apnea while having a very soft feeling of stimulation compared to a square wave having the same current and frequency.
- the stimulation generation means arbitrarily changes the density of the plurality of electric pulses constituting the electric pulse group, the low-frequency waveform into the therapist is preferable according to the density of the electric pulses. Can be distorted. Also, during the output period of the electric pulse group, the time width of each electric pulse is constant, and the rest period between the electric pulses is changed by the stimulation means, so that the wide electric pulse will not exist. As a result, the charging current for the equivalent capacitance of the therapist is supplied little by little, and the amount of charge gradually increases, so that the sensation of softer stimulation can be obtained.
- the stimulation generation means outputs the stimulation signal
- the waveform of each electric pulse group is distorted inside the treatment person, and the stimulation signal has a high frequency electric pulse superimposed on a signal similar to a low frequency sine wave. It becomes a waveform. Therefore, it is possible to effectively avoid apnea while having a very soft feeling of stimulation as compared to a square wave having the same current and frequency.
- the conductor including the electrode can be attached to a desired site, and the time and effort for attaching the pair of electrodes can be omitted.
- the pair of electrodes can be arranged side by side in the anteroposterior direction of the buttocks simply by sticking the sheet member to the buttocks of the therapist, the influence of the electroencephalogram due to the stimulation signal can be minimized. It is possible to correctly determine whether a person is sleeping or not.
- FIG. 1 is a block diagram showing an overall configuration of an apparatus according to a first embodiment of the present invention.
- 1 is a stabilized power supply that converts the AC input into a DC output in a stabilized state, and here an AC voltage of 100 V AC is converted to a DC voltage of 0 ° + 15 yen and 0 ° + 5 yen.
- Reference numeral 2 denotes a CPU (central processing unit) as a control means that operates with the DC +5 V DC voltage from the stabilized power supply 1 and the reference clock signal from the crystal oscillator 3.
- this CPU 2 incorporates input / output means, storage means, arithmetic processing means etc., and according to the control sequence stored in the storage means, a human body which is a living body having a predetermined pattern. Became to give)! / Scold.
- an operating means comprising a plurality of button type switches 48 and 18.
- an output side port of the CPU 2 is connected to a display means 11 such as an LED or an LCD, and also to determine the on time, off time, and amplitude of individual electric pulses in the stimulation signal.
- a variable output signal generating means 12 for generating a variable output signal and gates of two FETs 14 and 15 constituting the stimulus generating means 13 are connected respectively.
- the variable output signal generation means 12 operates with a DC voltage of DC + 15 V from the stable power source 1 and receives an interval signal which is a first control signal from the CPU 2 and outputs an output pulse.
- an amplitude setting unit 18 that determines the amplitude of an output pulse in response to an amplifier command signal that is a second control signal from the CPU 2. It is configured to supply the stimulus generation means 13 with a rectangular wave-like variable output signal in which each output pulse is amplitude-modulated in the range.
- the stimulus generation means 13 includes a variable output signal output from the variable output signal generation means 12 and an electric pulse generation signal, that is, a PWM (pulse width modulation) signal output from the CPU 2 to each of the FETs 14 and 15.
- a stimulation signal that repeats an energization period in which the electric pulse group occurs continuously or intermittently and a rest period in which the electric pulse group does not occur at a constant time in seconds.
- the stimulus generation means 13 in the present embodiment is configured to include a transformer 24 in which the primary side is isolated from the secondary side, in addition to the FETs 9 and 10 as switching means, and a primary winding of the transformer 24. 25 has its center tap connected to the variable output signal line of the variable output signal generating means 12, and a pair of output terminals 22A and 22B are provided at both ends of the secondary winding 26 that outputs the stimulation signal. Each connected.
- one drain of the primary winding 25 of the transformer 24 is connected to the drain of one FET 14 whose source is grounded, and the drain of the other FET 15 whose source is grounded is also connected to the primary winding 25 of the transformer 24. The other end is connected. Then, it is supplied to the gate which is the control terminal of the positive side PWM signal power FET 9 from the CPU 2, and the side PWM signal from the CPU 2 is supplied to the gate which is the control terminal of the FET 10.
- the CPU 2 has interval signal generation means 31 for generating an interval signal that determines the on time and the off time of the variable output signal as a functional configuration of a control sequence built in the storage means, and the amplitude of the variable output signal.
- An amplifier command signal generating means 32 for generating an amplifier command signal to be determined, a PWM signal generating means 33 for outputting a PWM signal to one of the gates of FETs 14 and 15, and operating conditions of variable output signals are stored.
- the operating condition management means 35 is provided to display the operating condition on the display means 11 as needed, and to update the setting of the operating condition.
- the operating conditions include the conduction period in which the on / off of the variable output signal repeatedly occurs and the occurrence of the on pulse, and the start of the output of the variable output signal (as a result, the stimulation signal).
- the amplitude of the variable output signal is gradually increased to a first time width until the amplitude stabilizes and the amplitude of the variable output signal after the first time width.
- variable output signal means 12 force on-pulse interval signal is generated, and a plurality of rectangular wave pulses from the PWM signal generating means 33 are generated.
- a rectangular wave pulse group as a force is configured to be output to the FETs 14 and 15 as a PWM signal.
- the rectangular wave pulse group at this time is preferably alternately output to any one of the FETs 14 and 15 every time a variable output signal means 12 force on pulse interval signal is generated, and each rectangular wave pulse group is generated. Until half of the energization period elapses from the rising of the rectangular wave pulse group. Gradually widens the time width of each square wave pulse and then gradually narrows the time width of each square wave pulse as the falling of the group of square wave pulses is approached. Generate a PWM signal.
- the interval signal generation means 31 repeatedly generates the on-noise interval signal during the energization period of the variable output signal set and stored in the operation condition management means 35, the pause of the variable output signal is generated. While the on-pulse interval signal is not generated in the period, the amplifier command signal generating means 32 has the first time width set and stored in the operating condition management means 35 and the time width after the first time width. Based on the amplitude of the variable output signal, the amplitude of the variable output signal is gradually increased from the start of the output of the variable output signal until the first time width elapses, and is set when the first time width has elapsed. An amplifier command signal that matches the amplitude is generated.
- the switch 4 corresponds to a fourth operation means and a fifth operation means, and each time the switch 4 is pressed, the output of the PWM signal, the variable output signal and thus the stimulation signal is started, Alternatively, an instruction to stop the output is alternately given to the CPU 2.
- the fourth operation means for starting the output of the stimulation signal and the fifth operation means for stopping the output of the stimulation signal may be configured with separate switches!
- the switch 5 corresponds to a first operation means for changing the amplitude of the electrical pulse to be output as a stimulation signal, and each time the switch 5 is pressed, the first set in the operation condition management means 35 is performed.
- the amplitude of the variable output signal after the time width can be changed.
- the switch 6 corresponds to a second operation means for varying the energization period generated by the electric pulse group included in the stimulation signal, and is set in the operating condition management means 35 each time the switch 6 is pressed.
- the power supply period of the variable output signal can be changed.
- the switch 7 corresponds to a third operation means for varying the resting period in which the electric pulse group contained in the stimulation signal is not generated, and is set in the operating condition management means 35 each time the switch 7 is pressed. It is possible to change the idle period of the variable output signal.
- the switch 8 is a sixth operation means for changing a first time width from the start of output of the variable output signal, that is, the output of the stimulation signal to stabilization of the amplitude of the electric pulse group to a constant level. Setting the operating condition management means 35 each time the switch 8 is pressed. You can now change the first time width!
- the apnea preventing stimulation apparatus in the present embodiment is not provided with a respiration detection means for monitoring the respiratory condition of the treated person. That is, the stimulation signal generated between the output terminals 22A and 22B of the conductor 21 is configured to be given regardless of the respiratory condition of the therapist.
- Reference numerals 22A and 22B denote the pair of output terminals described above, and the output terminals 22A and 22B are electrically connected to the stimulation generation means 13 housed in the device main body (not shown) by the connection cord 41.
- Reference numeral 42 denotes a sheet member which holds the output terminals 22A and 22B in a parallel state, and this sheet member 42 is a material having high flexibility and adhesiveness (for example, gel) so as to be attachable to and detachable from the buttocks P of the therapist. Material).
- the sheet member 42 in this case has the output terminals 22A, 22B arranged such that the output terminals 22A, 22B are juxtaposed in the front-rear direction of the buttocks P of the treating person. That is, when each electrode of the conductor 21 is disposed on the left and right of the buttocks P, the electroencephalogram is affected by the stimulation signal given to the electrode when the sleep state of the treatment person is judged by the electroencephalogram using this device. Can not be detected correctly.
- the output terminals 22A and 22B are arranged side by side in the front and back direction of the buttocks P.
- the electroencephalogram detector (not shown) can be used to minimize the influence of the patient, and allow the therapist to correctly identify the power and force that is asleep.
- the waveform at the top is the variable output signal from the output variable circuit 11, and in the following, the + side PWM signal given to the FET 14, the side PWM signal given to the FET 15 and the output terminal 22A, Each voltage waveform of the stimulation signal generated between 22B is shown.
- FIG. 3 shows the waveform of each part until the first time width T1 of the output start force of the stimulation signal elapses
- FIG. 4 shows the waveform of each part on the way to the first time width T1.
- 5 shows the waveform of each part after the first time width T1 has elapsed.
- the conductor 21 is attached to the buttocks P of the treating person by utilizing the adhesive property of the sheet member 42 in advance. At this time, the mounting of the conductor 21 is given directionality Since the sheet member 42 is formed in a horizontally long shape, the longitudinal direction of the sheet member 42 is inevitably attached in the left-right direction of the collar portion P, and the output terminal 22A in the front-rear direction of the collar portion P , 22B will be arranged side by side.
- the interval signal generating means 31 generates an output signal of an interval signal such that an output signal of a plurality of on-pulses is generated, and an output signal of an on-pulse is not generated at all during an idle period Tb.
- the amplifier command signal which gradually increases the amplitude A1 of the variable output signal until the first time width T1 (see FIG. 3) stored in the operating condition management means 35 elapses, while being repeatedly applied to the
- the signal generation unit 31 supplies the amplitude setting unit 18 of the variable output signal generation unit 12.
- the output variable of a plurality of on-pulses having a constant on-time tl and off-time t2 such that its amplitude A1 gradually increases
- the signal is output from the variable output signal generation means 18 to the center tap of the primary winding 25 of the transformer 24 during the conduction period Ta, when the idle period Tb is reached, the center tap of the primary winding 25 of the transformer 24 is The on-pulse output variable signal is not applied at all.
- the PWM signal generation means 33 sets, as the PWM signal, a rectangular wave pulse group consisting of a plurality of rectangular wave pulses during the on time tl during which the variable output signal generation means 18 outputs the variable output signal of on pulse. Output alternately to one of the gates of FETs 14 and 15.
- the PWM signal generating means of the CPU 2 generates a 33-wave power of the square wave pulse group as the + side PWM signal.
- the FET 14 is turned on, one end (dot side) of the primary winding 25 is grounded, and a voltage is induced at one end (dot side) of the secondary winding 26.
- the PWM signal generation means 33 of the CPU 2 sends a square wave pulse group to the FET 15 as an f-law PWM signal.
- the FET 15 When supplied, the FET 15 is turned on during the output period of each square wave pulse, the other end (non-dot side) of the primary winding 25 is grounded, and the other end of the secondary winding 26 Therefore, as shown also in Fig. 3 and Fig. 4, the on-pulse variable output signal is output from the variable output signal generation means 12 every time the conduction period Ta is generated, as shown in Figs.
- a stimulation signal such that a positive electrical pulse group S composed of a plurality of electrical pulses and a negative electrical pulse group S ′ composed of a plurality of electrical pulses are alternately generated with the off period T3 in between It is repeatedly applied between output terminals 22A and 22B.
- the amplitude A2 of each of the electric pulse groups S and S ′ is proportional to the amplitude A1 of the variable output signal. Therefore, immediately after the start of the stimulation signal output, ie, immediately after going to bed, the amplitude A2 of the electric pulse group S, S 'forming the stimulation signal becomes small after the time when it is hardly felt by the treatment person.
- the rate of increase of the amplitude A2 of the electric pulse group S, S ′ may be increased with time, rather than being constant. In this way, the amplitude A2 of the electric pulse group S, S 'does not increase so much for a while while the output start power of the stimulation signal is also for a while, and the therapist may fall into a sleep state without being affected by the stimulation signal. it can.
- the amplitude A2 of each electrical pulse in the same electrical pulse group S, S ′ is constant, and the amplitude A2 of each electrical pulse is a basic unit of the electrical pulse group S, S ′. Force that gradually increases with time Each electric pulse is used as a basic unit to Let's gradually increase the amplitude A2 of the electrical pulse.
- the amplitude A1 of the variable output signal approaches the amplitude of the variable output signal after the first time width set and stored in the operation condition management means 35, and forms a stimulation signal.
- the amplitude A2 of each electrical pulse is also stable and has a substantially constant value.
- the PWM signal generation unit 33 of the CPU 2 generates a plurality of rectangles each time the variable output signal generation unit 12 outputs a variable output signal of the on pulse during the conduction period Ta.
- a square wave pulse group consisting of wave pulses is alternately output to one of the gates of the FETs 14 and 15 as a PWM signal. Therefore, each time an on-pulse variable output signal is output from the variable output signal generating means 12 between the output terminals 22A and 22B, a plurality of electric pulse groups S consisting of a plurality of electric pulses and a plurality of electric pulses are generated.
- An electric pulse group S 'of negative polarity alternately occurs with the off period T3 in between, and is given to the buttock P of the patient as a stimulation signal.
- the PWM signal at this time has a time width t3 of each rectangular wave pulse until a half of the time width T2 for outputting the rectangular wave pulse group elapses from the rising of the rectangular wave pulse group.
- the time width t3 of each rectangular wave pulse gradually narrows as the rectangular wave pulse group approaches falling, and the electric pulse group is separated between the output terminals 22A and 22B.
- the time width t3 of each electric pulse gradually spreads until half of the time width T2 when the electric pulse group S, S' is output passes, and then the electric pulse group S, S, As the fall of S 'is approached, a stimulation signal is generated in which the time width t3 of the individual electrical pulses gradually narrows.
- pressing switch 4 to instruct to stop the output of the stimulation signal causes the variable output signal from variable signal generation means 12 to generate a PWM signal.
- the PWM signal from the means 33 is immediately stopped to output, and the output of the stimulation signal to the heel P is immediately cut off.
- the therapist can eliminate the discomfort caused by the stimulation signal being given indefinitely at awakening.
- you want to sleep after that you can only instruct CUP 2 to start outputting the stimulation signal by pressing switch 4 again, and since a strong stimulation signal is not given immediately after going to bed, this stimulation It can eliminate the negative effects of the signal on sleep.
- the repetition frequency f of the positive and negative electric pulse groups S and S ′ shown in FIG. 4 and FIG. 5 is 2.7 kHz
- the variable output signal and thus the conduction period of the stimulation signal is 30 seconds
- the rest period Tb is 10. It is a second.
- the frequency f, the conduction period Ta, and the rest period Tb can be arbitrarily changed by an external operation, since the degree of the apnea state is extremely individual differences.
- the pushing period of the switch 6 which is the second operating means makes it possible to easily change the conduction period Ta of the stimulation signal in which the electric pulse groups S and S 'are intermittently generated. can do.
- the gain of the input / output in the amplitude setting unit 18 is changed to configure the amplitude A1 of the variable output signal and thus the stimulation signal.
- the amplitude A2 of each electrical pulse generally increases or decreases.
- switch 5 can be adjusted to increase the amplitude A2.
- the conductor 21 is placed on the buttocks P of the treatment subject, and an electrical pulse is applied to the buttocks P of the treatment subject from this conduction member 21 to provide a stimulus for apnea prevention.
- a stimulation signal that repeats a given period of time a conduction period Ta in which an electric pulse group S, S ′ consisting of a plurality of electric pulses is generated and a rest period Tb in which the electric pulse group S, S ′ does not occur at all.
- the stimulus generating means 13 for outputting between the output terminals 22A and 22B of the conductor 21 is provided.
- the stimulation is repeated from stimulation generation means 13 via conductor 21 to conduction period Ta in which electric pulse group S, S ′ is generated, and rest period Tb in which electric pulse group S, S ′ is not generated.
- a signal is effectively given to the buttocks P of the therapist. Therefore, upper airway obstruction can be quickly avoided without having to monitor breathing during sleep.
- the stimulation signal for repeating the conduction period Ta and the rest period Tb of the electric pulse groups S and S ' is given to the buttock P of the treatment person regardless of the presence or absence of the treatment person's breathing, the treatment person receives this stimulation signal. Noticing that you can get a little more sleep. Therefore, it is possible to effectively give stimulation signals to the buttocks P of the therapist without disturbing the patient's sleep as much as possible without monitoring the respiratory condition.
- the electric pulse groups S and S ′ are generated at intervals of every off period T3, and the power off period T3 is not provided, and the electric pulse is continuously applied. It may be a stimulation signal that generates the pulse group S, S '.
- the switch 5 is provided as a first operation means capable of changing the amplitude A2 of the electric pulse contained in the stimulation signal.
- the switch 5 since the amplitude A2 of the electric pulse generated during the energization period Ta can be arbitrarily changed by the switch 5, it is possible to give an electric pulse of the optimum amplitude A2 to any therapeutic person. it can.
- the switch 6 is provided as a second operation means capable of changing the current application period Ta.
- the energization period Ta in which the electric pulse group S, S ′ is generated can be arbitrarily changed by the switch 6. Therefore, it is possible to give a stimulation signal having an optimum energization period Ta to any therapist.
- the switch 7 is provided as a third operation means capable of changing the pause period Tb. In this way, the conduction period Tb in which the electric pulse group S, S 'is not generated at all can be arbitrarily changed by the switch 7. Therefore, it is possible to give a stimulus signal having an optimal rest period Tb to any therapist.
- the fourth operation means for starting the output of the stimulation signal and the common switch 4 are provided as the fifth operation means for stopping the output of the stimulation signal.
- a stimulation signal can be output to the conductor 21 from that point on.
- treatment can be temporarily stopped by operating switch 4 again to stop the output of the stimulation signal.
- the switch 4 it is possible to freely select the start and stop of the output of the stimulation signal according to the intention of the therapist.
- the above switches 4 and 7 are not limited to the momentary type.
- the stimulation generation means 13 outputs a stimulation signal in which the amplitude A2 of the electrical pulse gradually increases until the first time width T1 of the output start force of the stimulation signal elapses. It is composed of
- a switch 8 is provided as a sixth operation means for varying the first time width T1.
- the first time width T1 can be changed by the switch 8, no call-to-breath state is assured when going to bed with any therapeutic person. It can give a stimulus signal to avoid.
- the switch 8 here is also not limited to the momentary type, needless to say.
- a stimulation signal in which the time width t3 of the plurality of electric pulses constituting the electric pulse group S, S ′ is varied is output.
- And means 13 for generating stimulation is output.
- the time width t3 of the individual electric pulses constituting the electric pulse group S, S ' is stimulated Since the generating means 13 is arbitrarily variable, it is possible to distort the low frequency waveform into the patient into a preferable state according to the increase or decrease of the time width t3 of the electric pulse.
- the stimulation generation means 13 is configured to alternately generate positive and negative electric pulse groups S and S ′ having the second time width T2 in the conduction period Ta. In this way, during the conduction period Ta, since the electric pulse groups S and S 'of alternating positive and negative are sequentially given to the buttocks P of the therapist, it is possible to reliably avoid the apnea condition.
- the time width t3 of each electric pulse is gradually extended until a half of the second time width T2 elapses from the rise of the electric pulse group S, S ′, and then the electric pulse is generated.
- the stimulation generation means 13 is configured to output a stimulation signal that gradually narrows the time width t3 of each electric pulse as the fall of the pulse groups S and S 'is approached.
- electric pulse groups S and S ′ having a second time width T 2 as a whole of a plurality of electric pulse forces appear alternately in the positive and negative directions for each period, and the electric pulse groups S and S ′ rise.
- the time width t3 of each electrical pulse gradually spreads until half of the second time width T2 elapses, and then the time of each electrical pulse is approached as the electrical pulse group S, S, approaches the falling edge.
- the stimulus generation means 13 outputs a stimulus signal so that the width t3 gradually narrows, repetition of electric pulse groups S and S 'including a plurality of signal components of high frequency (electrical pulse) is conducted from the conductor 21 to the stimulus.
- the conductor 21 in the present embodiment holds the output terminals 22A and 22B as a pair of electrodes to which the stimulation signal is applied and the output terminals 22A and 22B in the buttocks P of the therapist. It comprises a detachable adhesive sheet member 42.
- the conductor 21 including the output terminals 22A and 22B can be attached to a desired site simply by adhering the sheet member 42 to the buttocks P of the therapist, and the pair of output terminals 22A, The trouble of attaching the 22B can be omitted.
- the sheet member 42 is formed in a horizontally long shape so that the output terminals 22A and 22B are arranged so that the pair of output terminals 22A and 22B are juxtaposed in the front-rear direction of the buttocks P of the therapist. Place There is.
- the pair of output terminals 22A and 22B can be arranged side by side in the anteroposterior direction of the buttocks P. It can be suppressed, and the therapist can correctly identify the state of power and force that is asleep.
- a PDM (pulse density modulation) signal is applied to one of the gates of FETs 14 and 15 instead of PWM signal generating means 33 in the first embodiment.
- a PDM signal generating means 52 for outputting is provided.
- the PDM signal generation means 52 outputs a rectangular wave pulse group, which is also a plurality of rectangular wave norskers, to the FETs 14 and 15 as PDM signals in synchronization with the interval signal generation means 31 providing the on pulse interval signal.
- the rectangular wave pulse group at this time is preferably alternately output to one of the FETs 14 and 15 every time an on-pulse interval signal is generated from the variable output signal means 12, and the respective rectangular wave pulses are generated.
- the time interval (off time interval) between adjacent rectangular wave pulses is gradually narrowed until half of the conduction period elapses from the rising of the rectangular wave pulse group, and the pulse density per unit time is increased. As it rises and then approaches the falling edge of the square wave pulse group, the time interval between adjacent square wave pulses gradually increases, and the pulse density per unit time decreases. As to each rectangular wave Norusu occurs.
- the square wave pulses in this case have the same on-time width.
- the other configuration is the same as that of the first embodiment described above.
- FIG. 7 shows the waveforms of the respective parts on the way to the first time width T1
- FIG. 8 shows the waveforms of the respective parts after the first time width T1 has elapsed.
- the switch 4 when using the apparatus, first, after the conductor 21 is attached to the buttock P of the treatment person by the sheet member 42, the switch 4 is pushed to operate the stimulation signal Indicate the start of output of. Also in this case, the amplitude A2 of the electric pulse groups S and S 'forming the stimulation signal is small immediately after the start of the stimulation signal output, that is, immediately after going to bed. After that, as time passes and sleep state is reached, the amplitude A2 of the electric pulse group S, S 'increases to a level suitable for treatment.
- the PDM signal generation unit 33 of the CPU 2 generates a plurality of rectangular waves each time the variable output signal generation unit 12 outputs a variable output signal of on pulse during the conduction period Ta.
- a rectangular wave pulse group consisting of pulses is alternately output to one of the gates of the FETs 14 and 15 as a PDM signal. Therefore, each time a variable output signal of on-pulse is output from the variable output signal generation means 12 between the output terminals 22A and 22B, it comprises a plurality of electric pulse groups S of a plurality of electric pulses and a plurality of electric pulses. Negative electrical pulse groups S 'are generated alternately with an off period T3 and are given to the buttocks P of the therapist as a stimulation signal.
- the PDM signal at this time has an offset between the individual rectangular wave pulses until a half of the time width T2 in which the rectangular wave pulses are output is elapsed from the rising of the rectangular wave pulse group.
- the time width t4 gradually narrows and the pulse density increases, and then the off-time width t4 between the individual rectangular wave pulses gradually widens and the pulse density decreases as the pulse wave group approaches falling.
- the individual electric pulse is generated between the output terminals 22A and 22B until a half of the time width T2 in which the electric pulse group S, S 'is output is elapsed from the rising of the electric pulse group S, S'.
- the off-time width t4 gradually narrows and the pulse density increases, and then the off-time width t4 between individual electric pulses gradually spreads as the electric pulse group S, S 'approaches falling, and the pulse density increases.
- a stimulation signal is generated which is low. Then, this stimulation signal is energized via the conductor 21 to the lower part P of the treating person (human body) acting as a capacitive element such as a capacitor.
- the off time interval t4 between electric pulses constituting the stimulation signal is wide, ie, the frequency of the electric pulse is low, and in the part, the amount of charge / discharge for the equivalent capacitance of the human body is small. 22B, the change in the voltage waveform between them also becomes gentle. Conversely, in the part where the off time interval t4 between electric pulses is narrow, that is, where the frequency of the electric pulse is high, the amount of charge / discharge to the equivalent capacitance of the human body is large.
- the on-time width of each electrical pulse is constant, and the rest period (off-time interval t4) between the electrical pulses is changed by the stimulus generation means 13, the wide-width electrical pulse by the PWM modulation is not exist. Therefore, the charging current is supplied little by little to the equivalent capacitance of the human body, and the amount of charge (the amount of energization) gradually increases. Therefore, even with high-frequency electrical pulse components, it is possible to obtain a sensation that is softer and softer to the human body.
- each electric pulse group S, S ′ of time width T2 in the entire electric pulse force is positive and negative.
- the stimulus generation means 13 so as to output a stimulus signal in which t4 gradually spreads.
- time interval variable means capable of randomly varying the off time interval t4 is added to the control sequence of the CPU 2, for example, not only sine waves but also triangle waves and various distorted waves are given to the human body. It has a unique sensation different from sine waves.
- a stimulation signal in which the density of the plurality of electric pulses constituting the electric pulse group S, S ′ is varied is output.
- the stimulation generating means 13 is configured as follows.
- the stimulation generation means 13 arbitrarily changes the density of the plurality of electric pulses constituting the electric pulse group S, S ′, according to the high and low density of the electric pulses,
- the low frequency waveform can be distorted to a desirable state.
- the power of the electric pulse group S, S ' During the output period, the time width of each electrical pulse is constant, and the rest period (off time interval t4) between the electrical pulses is changed by the stimulus generation means 13, so that the wide electrical pulse does not exist.
- the charging current for the equivalent capacitance of the therapist is supplied little by little, and the amount of charge gradually increases, so that a sensation of softer sensation can be obtained.
- the electric pulse groups S and S ′ having the second time width T 2 in the current application period Ta are alternately generated in the positive and negative directions, and the rising of the electric pulse groups S and S ′ Stimulation in which the density of the electric pulses gradually increases until half of the time width T2 of 2 elapses, and then the density of the electric pulses gradually decreases as the electric pulse group S, S 'approaches falling.
- the stimulus generating means 13 is configured to output a signal.
- the stimulation generation means 13 When the stimulation generation means 13 outputs such a stimulation signal, the waveform of each of the electric pulse groups S and S ′ is distorted inside the human body, and the stimulation signal has a high frequency similar to a low frequency sine wave. It becomes the waveform which the electric pulse of the wave superimposed. Therefore, it is possible to effectively avoid an apnea while having a very soft feeling of stimulation compared to a rectangular wave having the same current and frequency.
- the present invention can be variously modified and implemented within the scope of the gist of the present invention which is not limited to the above embodiments.
- the stimulus generation means for outputting a desired stimulus signal to the conductor may be other than the configuration using the transformer and switch means as shown in this embodiment, and the control sequence of the CPU 2 can be changed as shown in FIG.
- the function of the output signal generation means 12 may be incorporated.
- Electrical pulses may be generated randomly.
- the electric pulse groups S, S may be configured by waveforms other than the PWM signal and the PDM signal.
- FIG. 1 is a block diagram showing an overall configuration of an apnea preventing stimulation apparatus according to a first embodiment of the present invention.
- FIG. 2 An explanatory view of a state in which a conductor is attached to the buttocks of the treating person in the first embodiment. Ru.
- FIG. 3 is a waveform diagram of each portion until the first time width has elapsed, of the output start power of the stimulation signal in the first embodiment.
- FIG. 4 is an enlarged waveform chart of each part on the way to the first time width in the first embodiment.
- FIG. 5 is an enlarged waveform chart of each part after the first time width has passed in the first embodiment.
- FIG. 6 is a block diagram showing the overall configuration of the apnea preventing stimulation apparatus in the second embodiment of the present invention.
- FIG. 7 is an enlarged waveform chart of each part on the way to the first time width in the second embodiment.
- FIG. 8 An enlarged waveform chart of each portion after the first time width has elapsed in the second embodiment.
Abstract
Description
Claims
Priority Applications (9)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
JP2006544751A JP4960704B2 (ja) | 2004-11-22 | 2004-11-22 | 無呼吸防止刺激装置 |
PCT/JP2004/017337 WO2006054359A1 (ja) | 2004-11-22 | 2004-11-22 | 無呼吸防止刺激装置 |
ES04822659.1T ES2476395T3 (es) | 2004-11-22 | 2004-11-22 | Aparato de estimulaci�n, para la prevención de la apnea |
CN2004800443396A CN101052440B (zh) | 2004-11-22 | 2004-11-22 | 防止无呼吸的刺激装置 |
KR1020077009064A KR101133807B1 (ko) | 2004-11-22 | 2004-11-22 | 무호흡 방지 자극 장치 |
US11/719,939 US20090216293A1 (en) | 2004-11-22 | 2004-11-22 | Apnea preventing stimulation apparatus |
EP04822659.1A EP1815882B1 (en) | 2004-11-22 | 2004-11-22 | Simulator for preventing apnea |
TW093138464A TWI289069B (en) | 2004-11-22 | 2004-12-10 | Stimulator for prevention of sleep apnea |
US13/463,374 US8473058B2 (en) | 2004-11-22 | 2012-05-03 | Apnea preventing stimulation apparatus |
Applications Claiming Priority (1)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
PCT/JP2004/017337 WO2006054359A1 (ja) | 2004-11-22 | 2004-11-22 | 無呼吸防止刺激装置 |
Related Child Applications (2)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US11/719,939 A-371-Of-International US20090216293A1 (en) | 2004-11-22 | 2004-11-22 | Apnea preventing stimulation apparatus |
US13/463,374 Continuation-In-Part US8473058B2 (en) | 2004-11-22 | 2012-05-03 | Apnea preventing stimulation apparatus |
Publications (1)
Publication Number | Publication Date |
---|---|
WO2006054359A1 true WO2006054359A1 (ja) | 2006-05-26 |
Family
ID=36406907
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
PCT/JP2004/017337 WO2006054359A1 (ja) | 2004-11-22 | 2004-11-22 | 無呼吸防止刺激装置 |
Country Status (8)
Country | Link |
---|---|
US (1) | US20090216293A1 (ja) |
EP (1) | EP1815882B1 (ja) |
JP (1) | JP4960704B2 (ja) |
KR (1) | KR101133807B1 (ja) |
CN (1) | CN101052440B (ja) |
ES (1) | ES2476395T3 (ja) |
TW (1) | TWI289069B (ja) |
WO (1) | WO2006054359A1 (ja) |
Cited By (7)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
JP2010057805A (ja) * | 2008-09-05 | 2010-03-18 | Techno Link Co Ltd | 生体刺激装置 |
JP2012239575A (ja) * | 2011-05-18 | 2012-12-10 | Hitohiko Tada | 電極パッド及びこれを備えた気道確保装置 |
WO2013113950A1 (es) | 2012-01-31 | 2013-08-08 | Torytrans, S.L. | Metodo y sistema de electroestimulacion para el tratamiento de la apnea del sueño |
JP5636129B1 (ja) * | 2014-05-16 | 2014-12-03 | 株式会社テクノリンク | 呼吸異常改善装置 |
JP2018504243A (ja) * | 2015-02-06 | 2018-02-15 | キングス カレッジ ロンドンKings College London | いびきおよび睡眠時無呼吸の治療のための装置 |
JP6488458B1 (ja) * | 2017-12-25 | 2019-03-27 | 株式会社テクノリンク | 生体刺激装置 |
JP2020203110A (ja) * | 2015-03-19 | 2020-12-24 | インスパイア・メディカル・システムズ・インコーポレイテッドInspire Medical Systems, Inc. | 閉塞性睡眠時無呼吸を治療する刺激 |
Families Citing this family (2)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
IL272381B2 (en) * | 2017-08-09 | 2024-04-01 | Torytrans S L | Methods for dealing with apnea and/or decreased breathing rate and a system for detecting these conditions |
KR20230173855A (ko) * | 2022-06-20 | 2023-12-27 | 서울대학교산학협력단 | 수면무호흡증용 전기 자극 치료 장치 및 방법 |
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- 2004-11-22 JP JP2006544751A patent/JP4960704B2/ja not_active Expired - Fee Related
- 2004-11-22 US US11/719,939 patent/US20090216293A1/en not_active Abandoned
- 2004-11-22 KR KR1020077009064A patent/KR101133807B1/ko not_active IP Right Cessation
- 2004-11-22 ES ES04822659.1T patent/ES2476395T3/es active Active
- 2004-11-22 WO PCT/JP2004/017337 patent/WO2006054359A1/ja active Application Filing
- 2004-11-22 CN CN2004800443396A patent/CN101052440B/zh not_active Expired - Fee Related
- 2004-11-22 EP EP04822659.1A patent/EP1815882B1/en not_active Expired - Fee Related
- 2004-12-10 TW TW093138464A patent/TWI289069B/zh not_active IP Right Cessation
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Cited By (17)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
JP2010057805A (ja) * | 2008-09-05 | 2010-03-18 | Techno Link Co Ltd | 生体刺激装置 |
JP2012239575A (ja) * | 2011-05-18 | 2012-12-10 | Hitohiko Tada | 電極パッド及びこれを備えた気道確保装置 |
WO2013113950A1 (es) | 2012-01-31 | 2013-08-08 | Torytrans, S.L. | Metodo y sistema de electroestimulacion para el tratamiento de la apnea del sueño |
US9114256B2 (en) | 2012-01-31 | 2015-08-25 | Torytrans, S.L | Electrostimulation method and system for the treatment of sleep apnea |
JP5636129B1 (ja) * | 2014-05-16 | 2014-12-03 | 株式会社テクノリンク | 呼吸異常改善装置 |
KR20150131909A (ko) * | 2014-05-16 | 2015-11-25 | 테크노 링크 컴파니 리미티드 | 호흡 이상 개선 장치 |
KR101647892B1 (ko) | 2014-05-16 | 2016-08-11 | 테크노 링크 컴파니 리미티드 | 호흡 이상 개선 장치 |
US9737708B2 (en) | 2014-05-16 | 2017-08-22 | Techno Link Co., Ltd. | Respiratory abnormality improvement apparatus |
JP2018504243A (ja) * | 2015-02-06 | 2018-02-15 | キングス カレッジ ロンドンKings College London | いびきおよび睡眠時無呼吸の治療のための装置 |
US11033738B2 (en) | 2015-02-06 | 2021-06-15 | King's College London | Apparatus for treatment of snoring and sleep apnoea |
JP2020203110A (ja) * | 2015-03-19 | 2020-12-24 | インスパイア・メディカル・システムズ・インコーポレイテッドInspire Medical Systems, Inc. | 閉塞性睡眠時無呼吸を治療する刺激 |
JP7229209B2 (ja) | 2015-03-19 | 2023-02-27 | インスパイア・メディカル・システムズ・インコーポレイテッド | 閉塞性睡眠時無呼吸を治療する刺激 |
JP6488458B1 (ja) * | 2017-12-25 | 2019-03-27 | 株式会社テクノリンク | 生体刺激装置 |
WO2019130715A1 (ja) * | 2017-12-25 | 2019-07-04 | 株式会社テクノリンク | 生体刺激装置 |
JP2019111204A (ja) * | 2017-12-25 | 2019-07-11 | 株式会社テクノリンク | 生体刺激装置 |
EP3616746A4 (en) * | 2017-12-25 | 2021-01-27 | Techno Link Co., Ltd. | DEVICE FOR STIMULATING LIVING BODIES |
US11191957B2 (en) | 2017-12-25 | 2021-12-07 | Techno Link Co., Ltd. | Living body stimulation device |
Also Published As
Publication number | Publication date |
---|---|
JPWO2006054359A1 (ja) | 2008-08-07 |
EP1815882A1 (en) | 2007-08-08 |
ES2476395T3 (es) | 2014-07-14 |
CN101052440B (zh) | 2012-03-28 |
KR101133807B1 (ko) | 2012-04-05 |
EP1815882A4 (en) | 2010-06-09 |
TWI289069B (en) | 2007-11-01 |
CN101052440A (zh) | 2007-10-10 |
TW200616688A (en) | 2006-06-01 |
KR20070090144A (ko) | 2007-09-05 |
JP4960704B2 (ja) | 2012-06-27 |
EP1815882B1 (en) | 2014-04-30 |
US20090216293A1 (en) | 2009-08-27 |
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