Source: https://patents.google.com/patent/JP6342247B2/en
Timestamp: 2019-10-21 06:20:09
Document Index: 556121455

Matched Legal Cases: ['arts 41', 'art 41', 'art 1', 'art 1', 'art 1', 'art 33', 'art 33', 'art 41', 'art 100']

JP6342247B2 - Ultrasonic energy treatment device - Google Patents
Ultrasonic energy treatment device Download PDF
JP6342247B2
JP6342247B2 JP2014147802A JP2014147802A JP6342247B2 JP 6342247 B2 JP6342247 B2 JP 6342247B2 JP 2014147802 A JP2014147802 A JP 2014147802A JP 2014147802 A JP2014147802 A JP 2014147802A JP 6342247 B2 JP6342247 B2 JP 6342247B2
JP2014147802A
JP2016022135A (en
定生 江幡
2014-07-18 Application filed by オリンパス株式会社 filed Critical オリンパス株式会社
2014-07-18 Priority to JP2014147802A priority Critical patent/JP6342247B2/en
2016-02-08 Publication of JP2016022135A publication Critical patent/JP2016022135A/en
2018-06-13 Publication of JP6342247B2 publication Critical patent/JP6342247B2/en
The present invention relates to ultrasonic energy treatment equipment.
2. Description of the Related Art Conventionally, an ultrasonic energy treatment apparatus that treats a lesion by irradiating a living tissue with ultrasonic energy is known (see, for example, Patent Document 1). The ultrasonic energy treatment device described in Patent Document 1 uses a wire, a spring, or the like between the ultrasonic irradiation surface of the insertion portion inserted into the blood vessel and the blood vessel wall in order to accurately irradiate the lesion with ultrasonic energy. While maintaining a desired distance, ultrasonic energy is irradiated from the ultrasonic irradiation surface toward the blood vessel wall.
International Publication No. 2012/052924
However, the therapeutic effect by irradiation with ultrasonic energy is greatly affected by the amount of heat energy taken away by blood flow. In addition, the speed of blood flow varies greatly depending on individual differences, differences in healing sites, and differences in pulsation timing. Therefore, just by making the distance between the ultrasonic irradiation surface of the insertion portion and the blood vessel wall constant as in the ultrasonic energy treatment device described in Patent Document 1, individual differences, healing sites or pulsation timing differences Due to the difference in the amount of heat energy taken away due to the blood flow, there is a problem that a therapeutic effect cannot be obtained due to insufficient cauterization, or burns are caused by excessive cauterization.
The present invention is intended to the amount of heat removed energy by the blood flow even when the or changed or different, to provide an ultrasonic energy treatment equipment which can obtain a constant therapeutic effect.
The present invention includes an insertion portion having an elongated shape that can be inserted into a blood vessel, an energy emission portion that is attached to the insertion portion and emits ultrasonic energy from inside the blood vessel to a living tissue outside the blood vessel, and the energy emission portion. Measured by the loss amount measurement unit for measuring the loss amount of the emitted ultrasonic energy due to the blood flow, and the loss amount measurement unit so that a desired amount of the ultrasonic energy is irradiated to the living tissue. and a control unit for controlling the energy emitting portion in response to the loss, and a comparison unit that compares the loss measured by the loss measuring unit with a predetermined first threshold value, the control section, the When the comparison unit determines that the loss amount exceeds the predetermined first threshold value, the intensity of the ultrasonic energy is increased and / or the emission time is increased, and the loss amount is equal to or less than the predetermined first threshold value. Judged If it was to provide an ultrasonic energy treatment device you shorten the intensity of ultrasound energy down and / or injection time.
According to the present invention, an inserted portion is inserted into a blood vessel, and ultrasonic energy is emitted from the energy emitting portion, thereby treating a lesioned portion of a living tissue outside the blood vessel. In this case, the control unit controls the energy emitting unit to irradiate the living tissue with a desired amount of ultrasonic energy according to the amount of ultrasonic energy loss due to the blood flow measured by the loss measuring unit. Regardless of the difference or change in the amount of heat energy taken away due to blood flow, the lesion can be sufficiently treated. Therefore, even when the amount of heat energy taken away by the blood flow differs or changes due to individual differences, healing sites, or pulsation timing, a certain therapeutic effect can be obtained.
In the above invention, a comparison unit that compares the loss amount measured by the loss amount measurement unit with a predetermined first threshold value is provided, and the control unit is configured to compare the loss amount with the predetermined first threshold value. When it is determined that the threshold value is exceeded, the intensity of the ultrasonic energy is increased and / or the injection time is lengthened. When the loss amount is determined to be equal to or less than the predetermined first threshold value, the intensity of the ultrasonic energy is increased. short lowered and / or the injection time.
When the heat energy taken away by the blood flow is large, the irradiation amount of ultrasonic energy to the living tissue is insufficient. On the other hand, when the heat energy taken away by the blood flow is small, the irradiation amount of ultrasonic energy to the living tissue is not insufficient. Therefore, if a value capable of distinguishing such a situation is set as the predetermined first threshold value, a desired amount can be applied to the living tissue based on the comparison result by the comparison unit regardless of the difference in the amount of heat energy taken away by the blood flow. The lesion can be treated by irradiating ultrasonic energy.
In the above invention, when the comparison unit determines that the loss amount is equal to or less than the predetermined first threshold value, the comparison unit compares the loss amount with a predetermined second threshold value that is smaller than the predetermined first threshold value. The control unit may stop the irradiation of the ultrasonic energy when the loss is determined to be equal to or less than the predetermined second threshold by the comparison unit.
When the heat energy taken away by the blood flow is very small, that is, when there is almost no influence of the blood flow, the insertion portion and the blood vessel wall may not be maintained at a desired distance. Therefore, if a value that can identify such a situation is set as the predetermined second threshold value, the living tissue outside the treatment target is damaged by the irradiation of ultrasonic energy due to a shift in the distance between the insertion portion and the blood vessel wall. Can be prevented.
The present invention includes an insertion portion having an elongated shape that can be inserted into a blood vessel, an energy emission portion that is attached to the insertion portion and emits ultrasonic energy from inside the blood vessel to a living tissue outside the blood vessel, and the energy emission portion. Measured by the loss amount measurement unit for measuring the loss amount of the emitted ultrasonic energy due to the blood flow, and the loss amount measurement unit so that a desired amount of the ultrasonic energy is irradiated to the living tissue. a control unit for controlling the energy emitting portion in response to the loss, and a pulse period detecting section for detecting a pulse period of blood flow, the control unit, the waveform of the pulse period detected by the pulse period detecting unit When the loss amount measured by the loss amount measurement unit decreases, the intensity of the ultrasonic energy is lowered and / or the injection time is shortened, and the measured loss amount is increased. Serial to provide an ultrasonic energy treatment device to increase the strength of the raised and / or injection times of ultrasonic energy.
The amount and speed of blood flow change greatly due to the pulsation, the blood flow is the fastest during the contraction period of the pulsation, and the blood flow is almost zero during the diffusion period of the pulsation. For this reason, with the periodic change of pulsation, the loss amount of ultrasonic energy measured by the loss amount measurement unit also changes periodically. Therefore, by configuring in this way, it is possible to follow the change in blood flow due to pulsation and control the energy emitting unit to prevent excessive irradiation or insufficient irradiation of ultrasonic energy.
The present invention includes an insertion portion having an elongated shape that can be inserted into a blood vessel, an energy emission portion that is attached to the insertion portion and emits ultrasonic energy from inside the blood vessel to a living tissue outside the blood vessel, and the energy emission portion. Measured by the loss amount measurement unit for measuring the loss amount of the emitted ultrasonic energy due to the blood flow, and the loss amount measurement unit so that a desired amount of the ultrasonic energy is irradiated to the living tissue. A controller that controls the energy emitting unit according to a loss amount, and the loss amount measuring unit detects upstream of the irradiation position of the ultrasonic energy emitted by the energy emitting unit in the blood flow direction. The amount of loss is measured based on the flow rate of blood obtained in this way, and the control unit detects the flow rate detection position in the blood from which the flow rate has been detected by the loss amount measurement unit. To provide an ultrasonic energy treatment device for controlling the energy emitting portion at different timings by the time lag to reach the irradiation position of the energy.
The amount and speed of the blood flow change according to the pulsation timing and the state of the patient, and the amount of heat energy taken away by the blood flow in the ultrasonic energy changes as the blood flow changes. Therefore, by configuring in this way, the energy emitting unit can be controlled at a timing corresponding to an actual change in blood flow, and excessive irradiation or insufficient irradiation of ultrasonic energy can be prevented.
A reference example of the present invention is an energy injection process for injecting ultrasonic energy from inside a blood vessel to a living tissue outside the blood vessel, and a loss amount measurement for measuring a loss amount due to blood flow of the ultrasonic energy emitted by the energy injection process. And the energy ejection step includes the step of measuring the ultrasonic energy according to the loss measured by the loss measurement step so that the desired amount of the ultrasonic energy is irradiated onto the living tissue. An ultrasonic energy treatment method for adjusting ejection is provided.
According to the reference example of the present invention , the lesioned part of the living tissue outside the blood vessel is treated by ejecting ultrasonic energy from inside the blood vessel through the energy ejection process. In this case, the energy injection process adjusts the emission of the ultrasonic energy according to the loss amount of the ultrasonic energy due to the blood flow measured in the loss measurement process, and the living tissue is irradiated with the desired amount of ultrasonic energy. This makes it possible to sufficiently treat the lesion regardless of the difference or change in the amount of heat energy taken away by the blood flow. Therefore, even when the amount of heat energy taken away by the blood flow differs or changes due to individual differences, healing sites, or pulsation timing, a certain therapeutic effect can be obtained.
The reference example includes a comparison step of comparing the loss amount measured by the loss amount measurement step with a predetermined first threshold value, and the energy injection step includes the comparison step, and the loss amount is the predetermined amount. If it is determined that the first threshold value is exceeded, the intensity of the ultrasonic energy is increased and / or the injection time is lengthened. If the loss amount is determined to be equal to or less than the predetermined first threshold value, the ultrasonic energy is increased. It is also possible to reduce the strength and / or shorten the injection time.
By configuring in this way, if a value that can distinguish the excess or deficiency of the irradiation amount of ultrasonic energy on the living tissue is set as the predetermined first threshold, regardless of the difference in the amount of heat energy taken away by the blood flow, A lesion can be treated by irradiating a living tissue with a desired amount of ultrasonic energy based on the comparison result of the comparison step.
In the above reference example , when the comparison step determines that the loss amount is equal to or less than the predetermined first threshold value, the loss amount is compared with a predetermined second threshold value that is smaller than the predetermined first threshold value. The energy injection step may stop the irradiation of the ultrasonic energy when the loss amount is determined to be equal to or less than the predetermined second threshold value by the comparison step.
By configuring in this way, the distance interval between the insertion portion and the living tissue can be set by setting a value that can certify the situation where the insertion portion and the living tissue are not maintained at a desired distance interval as the predetermined second threshold value. By shifting, it is possible to prevent the biological tissue outside the treatment target from being damaged by the irradiation of ultrasonic energy.
The reference example of the present invention detects an energy injection process for injecting ultrasonic energy from inside a blood vessel to a living tissue outside the blood vessel, and a temporal change in a loss value due to blood flow of the ultrasonic energy emitted by the energy injection process. A loss value detection step, and when the loss value detected by the loss value detection step is reduced, the energy emission step reduces the intensity of the ultrasonic energy and / or shortens the injection time, and the detected When the loss value increases, an ultrasonic energy treatment method is provided that increases the intensity of the ultrasonic energy and / or lengthens the injection time in the energy injection step.
According to this reference example , a lesion can be treated by irradiating a living tissue with a desired amount of ultrasonic energy in accordance with a change in the amount of heat energy taken away by blood flow.
The reference example includes a pulsation cycle detection step for detecting a pulsation cycle of blood flow, and the energy emission step emits ultrasonic energy in synchronization with the waveform of the pulsation cycle detected by the pulsation cycle detection step. In addition to controlling, if the loss value detected by the loss value detection step decreases, the intensity of the ultrasonic energy is reduced and / or the injection time is shortened, and if the detected loss value increases, the super The intensity of the sonic energy may be increased and / or the injection time may be increased.
With such a configuration, it is possible to control the amount of ultrasonic energy applied to the living tissue following the change in blood flow, and to prevent excessive irradiation or insufficient irradiation of ultrasonic energy.
In the reference example , the loss value detection step is based on the blood flow velocity obtained by detecting upstream of the irradiation position of the ultrasonic energy emitted by the energy emission step in the blood flow direction. In the energy injection process, the flow velocity detection position in the blood where the flow velocity is detected by the loss value detection process reaches the irradiation position of the ultrasonic energy emitted by the energy injection process. It is also possible to adjust the emission of the ultrasonic energy by shifting the timing by the time delay until.
By comprising in this way, ejection | emission of ultrasonic energy can be controlled at the timing corresponding to the actual change of a blood flow, and it can prevent excessive irradiation and irradiation shortage of ultrasonic energy.
According to the present invention, there is an effect that a certain therapeutic effect can be obtained even when the amount of heat energy taken away by the blood flow is different or changes.
1 is a block diagram showing an ultrasonic energy therapy apparatus according to a first embodiment of the present invention. It is the figure which looked at the radial direction and the figure which looked at the insertion part of the ultrasonic energy treatment apparatus of FIG. 1 inserted in the blood vessel in the radial direction. It is a flowchart explaining the ultrasonic energy treatment method which concerns on 1st Embodiment of this invention. It is a timing chart which shows the relationship between the blood flow change of the temperature measurement sensor vicinity, the detection temperature of a temperature measurement sensor, the waveform of the detection temperature input into a smoothing circuit part, and the waveform of the detection temperature output from a smoothing circuit part. It is a flowchart explaining the ultrasonic energy treatment method which concerns on the modification of 1st Embodiment of this invention. It is a block diagram which shows the ultrasonic energy treatment process which concerns on 2nd Embodiment of this invention. It is a figure which shows the pulsation period detection part of the ultrasonic energy treatment apparatus which concerns on 2nd Embodiment of this invention. It is a flowchart explaining the ultrasonic energy treatment process which concerns on 2nd Embodiment of this invention. It is a timing chart which shows the relationship between the blood flow change of the temperature measurement sensor vicinity, the detection temperature of a temperature measurement sensor, the output signal of a comparator, a pulsation period pulse, and the output of ultrasonic energy. It is the figure which looked at the insertion part of the ultrasonic energy treatment apparatus which concerns on 3rd Embodiment of this invention inserted in the blood vessel, and looked at the radial direction, and the longitudinal direction. It is a block diagram which shows the ultrasonic energy treatment apparatus of FIG. It is a figure which shows the upstream temperature sensor determination part and time measurement part of FIG. It is a timing chart which shows the time change of the temperature detected by two temperature sensors. When the temperature sensor 13A is arranged upstream in the blood flow direction, the detected temperature of the temperature sensor 13A, the detected temperature of the temperature sensor 13B, the output of the pulsation cycle detector 41A, the output of the pulsation cycle detector 41B, and the pulsation It is a timing chart which shows the relationship of the output of the difference time signal between the period detection parts 41A and 41B, a pulsation period pulse, and ultrasonic energy. Detection temperature of temperature measurement sensor 13B, detection temperature of temperature measurement sensor 13A, output of temperature measurement sensor 13B, output of temperature measurement sensor 13A, pulsation cycle detection when temperature measurement sensor 13B is arranged upstream in the blood flow direction It is a timing chart which shows the output time difference signal between part 41A, 41B, the pulsation period pulse, and the output of ultrasonic energy. It is a flowchart explaining the ultrasonic energy treatment process which concerns on 3rd Embodiment of this invention. It is the figure which looked at the insertion part of the ultrasonic energy treatment apparatus concerning the modification of each embodiment of this invention inserted in the blood vessel, and the figure seen in the radial direction.
An ultrasonic energy treatment device and an ultrasonic energy treatment method according to a first embodiment of the present invention will be described below with reference to the drawings.
As shown in FIGS. 1 and 2, an ultrasonic energy treatment apparatus 100 according to the present embodiment includes an elongated substantially cylindrical insertion portion 1 that can be inserted into a blood vessel of a patient, and a main body portion 3 that supports the insertion portion 1. And.
The insertion unit 1 includes a piezoelectric element (energy emitting unit) 11 that generates ultrasonic energy, and a temperature sensor (energy loss measuring unit) 13 such as a thermistor that can detect the speed of blood flow in the blood vessel. Is provided.
The piezoelectric element 11 can be focused with high density by generating ultrasonic energy from an exit surface formed in a concave shape. The ultrasonic energy emitted from the piezoelectric element 11 can be treated by heating or cauterizing the lesioned part by changing to thermal energy at a focal position that matches the lesioned part of the living tissue. Further, the piezoelectric element 11 is attached to the insertion portion 1 with the emission surface facing outward in the radial direction of the insertion portion 1, and is connected to the main body portion 3 by a signal line 15.
The temperature sensor 13 is connected to the main body 3 by a signal line 17 and generates heat when energized. The resistance value of the temperature measuring sensor 13 is increased when the generated heat is taken away by the cooling action by the blood flow.
In addition, a balloon 19 that can fix the insertion portion 1 in a positioned state in a blood vessel is attached to the insertion portion 1. The balloon 19 is disposed on the proximal end side with respect to the piezoelectric element 11 and the temperature sensor 13. The balloon 19 is filled with a liquid or a gas so as to be inflated outward from each of the two locations shifted 180 degrees in the circumferential direction of the insertion portion 1. Accordingly, the balloon 19 is inflated in two opposite directions from the insertion portion 1 in the blood vessel and brought into contact with the blood vessel wall, thereby fixing the insertion portion 1 in a positioned state in the radial direction without obstructing blood flow. Can be done.
The main body 3 includes a signal generation unit 21 that generates a reference waveform signal of power, an amplification unit 23 that amplifies the reference waveform signal generated by the signal generation unit 21 and applies the amplified signal to the piezoelectric element 11, and a temperature sensor 13. A temperature detection unit (loss amount measurement unit) 25 that detects temperature, a smoothing circuit unit 27 that smoothes the waveform of the detected temperature detected by the temperature detection unit 25, and a storage unit 29 that stores a predetermined threshold value related to temperature The comparison unit 31 that compares the detected temperature smoothed by the smoothing circuit unit 27 with a predetermined threshold value stored in the storage unit 29, and the signal generation unit 21 and the amplification unit 23 based on the comparison result by the comparison unit 31. And a control unit 33 for controlling.
The temperature detector 25 measures the resistance value of the temperature measuring sensor 13 by measuring the weak current supplied to the temperature measuring sensor 13. Since the resistance value of the temperature measurement sensor 13 is increased by depriving the heat, the temperature of the temperature measurement sensor 13 can be indirectly detected by measuring the resistance value of the temperature measurement sensor 13. Further, since the rate of increase in the resistance value of the temperature sensor 13 has a unique relationship with the flow velocity of the fluid, the speed of the blood flow can be detected by measuring the resistance value of the temperature sensor 13. The amount of loss of ultrasonic energy due to blood flow can be determined from the speed of blood flow.
Therefore, by detecting the temperature of the temperature sensor 13 with the temperature sensor 13 and the temperature detector 25, the amount of loss due to blood flow of ultrasonic energy can be indirectly measured. The temperature detector 25 sends the measured resistance value detection result of the temperature sensor 13 to the smoothing circuit 27 as a detected temperature.
The smoothing circuit unit 27 smoothes the waveform of the detected temperature sent from the temperature detection unit 25 and sends it to the comparison unit 31.
The storage unit 29 stores a threshold value α and a threshold value β that is larger than the threshold value α. When the temperature detected by the temperature sensor 13 is high, that is, when the loss amount of ultrasonic energy is small, the blood flow is slow, and the thermal energy carried away by the blood flow is small in the ultrasonic energy emitted from the piezoelectric element 11. It will be. In this case, the irradiation amount of ultrasonic energy to the living tissue is not insufficient. On the other hand, when the temperature detected by the temperature sensor 13 is low, that is, when the loss amount of ultrasonic energy is large, the blood flow is fast, and the thermal energy taken away by the blood flow out of the ultrasonic energy emitted from the piezoelectric element 11. Will be big. In this case, the irradiation amount of ultrasonic energy to the living tissue is insufficient. Therefore, the storage unit 29 is configured to store, as the threshold value α, the minimum value of the temperature detected by the temperature measurement sensor 13 in a situation where the irradiation amount of ultrasonic energy to the living tissue is sufficient.
Further, when the temperature detected by the temperature sensor 13 is very high, that is, when the loss amount of ultrasonic energy is very small, there is almost no influence of blood flow, and the insertion portion 1 and the blood vessel wall are at a desired distance interval. May not be kept. In this case, the amount of ultrasonic energy applied to the living tissue becomes excessive. Therefore, the storage unit 29 is configured to store, as the threshold value β, the maximum value of the temperature detected by the temperature measuring sensor 13 in a state where the insertion unit 1 and the blood vessel wall are maintained at a desired distance interval.
The detected temperature of the temperature sensor 13 is replaced with the amount of ultrasonic energy loss, and the maximum amount of ultrasonic energy loss in a situation where the amount of ultrasonic energy irradiated to the living tissue is sufficient corresponding to the threshold value α. The threshold value γ (first threshold value) is set, and the minimum value of the loss amount of ultrasonic energy in the situation where the insertion portion 1 and the blood vessel wall are maintained at a desired distance interval corresponding to the threshold value β is the threshold value δ. Assuming (second threshold), the relationship of threshold γ> threshold δ is established. Therefore, the relationship between the threshold α and the threshold β and the relationship between the threshold γ and the threshold δ are reversed.
The comparison unit 31 compares the detected temperature of the smoothed temperature measuring sensor 13 sent from the smoothing circuit unit 27 with the threshold value α stored in the storage unit 29, and sends the comparison result to the control unit 33. It has become. In addition, when the comparison unit 31 determines that the temperature detected by the temperature sensor 13 is equal to or higher than the threshold value α, the comparison unit 31 compares the temperature detected by the temperature sensor 13 with the threshold value β and sends the comparison result to the control unit 33. It has become.
When it is determined by the comparison unit 31 that the temperature detected by the temperature measurement sensor 13 is lower than the threshold value α, that is, when the loss amount due to blood flow of ultrasonic energy is larger than the threshold value γ described above, The signal generation unit 21 is controlled to extend the emission time of the ultrasonic energy so that a desired amount of ultrasonic energy is irradiated to the living tissue.
In addition, when the comparison unit 31 determines that the temperature detected by the temperature measuring sensor 13 is equal to or higher than the threshold value α, that is, when the amount of loss due to blood flow of ultrasonic energy is equal to or lower than the threshold value γ, On the other hand, the emission time of ultrasonic energy from the signal generation unit 21 is shortened so that a desired amount of ultrasonic energy is irradiated.
In addition, when the comparison unit 31 determines that the temperature detected by the temperature sensor 13 is equal to or higher than the threshold value β, that is, when the amount of loss due to blood flow of ultrasonic energy is equal to or lower than the threshold value δ, the ultrasonic energy The signal generator 21 is controlled so as to stop the irradiation.
Next, the ultrasonic energy treatment method according to this embodiment will be described.
The ultrasonic energy treatment method according to the present embodiment is based on an energy injection step (step SA4) for injecting ultrasonic energy from inside a blood vessel to a living tissue outside the blood vessel, and a blood flow of ultrasonic energy emitted by the energy injection step. The temperature detection step (loss amount measurement step, step SA1) for detecting the amount of loss, that is, the temperature of the temperature sensor 13, and the detected temperature of the temperature sensor 13 detected by the temperature detection step are compared with a predetermined threshold value. The comparison process (step SA2, step SA5) is included.
In the comparison step, the temperature detected by the temperature measurement sensor 13 detected in the temperature detection step is compared with the threshold value α. Further, in the comparison step, when it is determined that the temperature detected by the temperature measuring sensor 13 is equal to or higher than the threshold α, the threshold β higher than the threshold α is compared with the temperature detected by the temperature measuring sensor 13.
In the energy injection process, the injection of the ultrasonic energy is adjusted according to the detected temperature of the temperature sensor 13 measured in the temperature detection process so that a desired amount of ultrasonic energy is irradiated to the living tissue. It has become. Specifically, in the energy injection process, when it is determined by the comparison process that the temperature detected by the temperature sensor 13 is lower than the threshold value α, the emission time of the ultrasonic energy is lengthened, and the temperature detected by the temperature sensor 13 is When it is determined that the threshold value α is greater than or equal to the threshold value α, the ultrasonic energy emission time is shortened. Further, in the energy injection process, when the temperature detected by the temperature sensor 13 is determined to be equal to or higher than the threshold value β by the comparison process, the irradiation of ultrasonic energy is stopped.
The operation of the ultrasonic energy therapy apparatus 100 and the ultrasonic energy therapy method configured as described above will be described with reference to the flowchart of FIG.
In order to treat a patient's lesion by the ultrasonic energy treatment apparatus 100 and the ultrasonic energy treatment method according to the present embodiment, the temperature sensor 13 is energized and the insertion part 1 is inserted into the patient's blood vessel.
The insertion portion 1 is arranged so that the exit surface of the piezoelectric element 11 faces the lesioned portion of the living tissue through the blood vessel wall, the balloon 19 is inflated, and the insertion portion 1 is fixed at this position in a positioned state. .
Next, the temperature detector 25 measures the weak current supplied to the temperature sensor 13, and detects the temperature of the temperature sensor 13 (step SA1, temperature detection step). The waveform of the temperature detected by the temperature sensor 13 detected by the temperature detection unit 25 is smoothed by the smoothing circuit unit 27 and sent to the comparison unit 31 as shown in FIG. FIG. 4 shows blood flow changes in the vicinity of the temperature sensor 13, the detected temperature of the temperature sensor 13, the waveform of the detected temperature input to the smoothing circuit unit 27, and the waveform of the detected temperature output from the smoothing circuit unit 27. Show.
Next, the comparison unit 31 compares the detected temperature of the temperature measurement sensor 13 sent from the smoothing circuit unit 27 with the threshold value α stored in the storage unit 29 (step SA2, comparison process). When the comparison unit 31 determines that the temperature detected by the temperature sensor 13 is lower than the threshold value α (step SA2 “Yes”), the blood flow is fast and the heat energy taken away by the blood flow is large.
In this case, the signal generation unit 21 is controlled by the control unit 33, and the emission time of the ultrasonic energy emitted from the piezoelectric element 11 is extended so that a desired amount of ultrasonic energy is irradiated onto the living tissue ( Step SA3). As a result, ultrasonic energy is emitted from the piezoelectric element 11 for a longer time than the initial setting (step SA4, energy injection process), and the loss of ultrasonic energy due to blood flow is compensated, and a desired amount of ultrasonic energy is applied to the living tissue. Is irradiated. Therefore, the lesioned part can be sufficiently treated.
On the other hand, if the comparison unit 31 determines that the temperature detected by the temperature sensor 13 is equal to or higher than the threshold value α (step SA2 “No”), the blood flow is slow and the heat energy carried away by the blood flow is small. In this case, the comparison unit 31 compares the detected temperature of the temperature measurement sensor 13 with the threshold value β stored in the storage unit 29 (step SA5, comparison process).
When the comparison unit 31 determines that the temperature detected by the temperature sensor 13 is lower than the threshold value β (step SA5 “Yes”), the distance between the insertion unit 1 and the blood vessel wall is normally maintained. become. In this case, the signal generation unit 21 is controlled by the control unit 33, and the emission time of the ultrasonic energy from the piezoelectric element 11 is shortened so that a desired amount of ultrasonic energy is irradiated to the living tissue (step SA6). ). Thereby, ultrasonic energy is ejected from the piezoelectric element 11 for a shorter time than the initial setting (step SA4, energy ejection process), and a desired amount of ultrasonic energy is irradiated to the living tissue without excessive irradiation. Therefore, the lesioned part can be sufficiently treated.
On the other hand, if the comparison unit 31 determines that the temperature detected by the temperature sensor 13 is equal to or higher than the threshold value β (step SA5 “No”), the distance between the insertion unit 1 and the blood vessel wall is not maintained normally. The insertion portion 1 is close to or in contact with the blood vessel wall. In this case, the signal generator 21 is controlled by the controller 33, and the irradiation of ultrasonic energy is stopped (step SA7, energy emission process). Thereby, it can prevent that the biological tissue outside a treatment object is damaged by irradiation of ultrasonic energy by the distance interval of the insertion part 1 and the blood vessel wall shifting.
As described above, according to the ultrasonic energy therapy apparatus 100 and the ultrasonic energy therapy method according to the present embodiment, the control unit 33 determines the temperature of the temperature sensor 13 based on the weak current waveform. By controlling the emission time of the ultrasonic energy from the piezoelectric element 11 so that a desired amount of ultrasonic energy is irradiated to the living tissue, the lesioned part is affected regardless of the difference or change in the amount of heat energy taken away by the blood flow. Can be fully treated. Therefore, even when the amount of heat energy taken away by the blood flow differs or changes due to individual differences, healing sites, or pulsation timing, a certain therapeutic effect can be obtained.
In the present embodiment, a predetermined threshold value is set, and the ultrasonic energy is binarized and irradiated with the predetermined threshold value as a boundary. Instead, for example, based on flow velocity detection data, The intensity of ultrasonic energy and / or the irradiation time may be changed seamlessly.
That is, in the present embodiment, the control unit 33 controls the emission time of the ultrasonic energy from the piezoelectric element 11 and the energy emission process adjusts the emission time of the ultrasonic energy. As a modified example, the control unit 33 controls the amplification unit 23 to control the intensity of ultrasonic energy emitted from the piezoelectric element 11 so that a desired amount of ultrasonic energy is irradiated to the living tissue. Also good. Further, the energy injection step may adjust the intensity of the ultrasonic energy so that a desired amount of ultrasonic energy is irradiated to the living tissue.
In this case, as shown in the flowchart of FIG. 5, when the comparison unit 31 determines in step SA2 that the temperature detected by the temperature measurement sensor 13 is lower than the threshold value α (step SA2 “Yes”), control is performed. The amplifying unit 23 is controlled by the unit 33, and the intensity of the ultrasonic energy emitted from the piezoelectric element 11 is increased to ε (W / cm 2 ) so that a desired amount of ultrasonic energy is applied to the living tissue. Step SB3). As a result, ultrasonic energy is emitted from the piezoelectric element 11 with a stronger intensity than the initial setting (step SA4, energy injection process), and the loss of ultrasonic energy due to blood flow is compensated for to a desired amount of ultrasonic waves in the living tissue. Energy is irradiated.
In step SA5, when the comparison unit 31 determines that the temperature detected by the temperature sensor 13 is lower than the threshold value β (step SA5 “Yes”), the control unit 33 controls the amplification unit 23, and the living body. The intensity of the ultrasonic energy emitted from the piezoelectric element 11 is reduced to ζ (W / cm 2 ) so that the tissue is irradiated with a desired amount of ultrasonic energy (step SB6). Note that the intensity of the ultrasonic energy is ε> ζ. As a result, the ultrasonic energy is emitted from the piezoelectric element 11 with a weaker intensity than the initial setting (step SA4, energy injection process), and a desired amount of ultrasonic energy is irradiated to the living tissue without excessive irradiation. .
Also according to this modification, a certain therapeutic effect can be obtained even when the amount of heat energy taken away by the blood flow changes or changes due to individual differences, healing sites, or pulsation timing differences.
Next, an ultrasonic energy treatment apparatus and an ultrasonic energy treatment method according to the second embodiment of the present invention will be described.
As shown in FIG. 6, the ultrasonic energy treatment apparatus 200 according to the present embodiment replaces the smoothing circuit unit 27, the comparison unit 31, and the storage unit 29 with a pulsation cycle detection unit (pulsation detection unit) 41, an A / The second embodiment is different from the first embodiment in that it includes a D conversion unit 43 and a FIFO (First In First Out memory) memory 45. The ultrasonic energy treatment method according to this embodiment is different from the first embodiment in that it includes a pulsation cycle detection step.
Hereinafter, the same reference numerals are given to the portions having the same configurations as those of the ultrasonic energy treatment device and the ultrasonic energy treatment method according to the first embodiment, and the description thereof will be omitted.
The temperature detection unit 25 is configured to send a temperature detection signal related to the temperature detected by the temperature measurement sensor 13 to both the pulsation cycle detection unit 41 and the A / D conversion unit 43.
The pulsation cycle detector 41 detects the pulsation cycle based on the temperature detected by the temperature sensor 13 sent from the temperature detector 25. That is, as shown in FIG. 7, the pulsation cycle detection unit 41 includes a comparator 47, which compares the temperature detection signal of the temperature measurement sensor 13 sent from the temperature detection signal by the comparator 47, thereby calculating the pulsation cycle. The pulsation synchronizing pulse shown is generated. The pulsation cycle pulse generated by the pulsation cycle detection unit 41 is sent to the control unit 33.
The A / D converter 43 AD converts the temperature detection signal of the temperature sensor 13 sent from the temperature detector 25.
The FIFO memory 45 temporarily stores the temperature detection signal AD-converted by the A / D conversion unit 43 for each pulsation period in time-series order, and repeatedly updates every pulsation period. The FIFO memory 45 always stores a temperature detection signal for one pulsation cycle.
The control unit 33 reads the temperature detection signal for one pulsation period stored in the FIFO memory 45 from the oldest in chronological order. Further, the control unit 33 synchronizes with the waveform of the pulsation cycle pulse sent from the pulsation cycle detection unit 41 on the basis of the temperature detection signal read from the FIFO memory 45, and exceeds the intensity that is inversely proportional to the level of the temperature detection signal. An output control signal for emitting sonic energy is generated.
Specifically, the control unit 33 synchronizes with the waveform of the pulsation cycle pulse when the detection temperature of the temperature measurement sensor 13 is increased so that a desired amount of ultrasonic energy is irradiated to the living tissue. That is, when the amount of ultrasonic energy loss is reduced, the intensity of ultrasonic energy is lowered, and when the temperature detected by the temperature sensor 13 is lowered, that is, when the amount of ultrasonic energy loss is increased, the ultrasonic energy is reduced. An output control signal for increasing the energy intensity is sent to the amplifying unit 23.
The amplifier 23 changes the amplification factor of the voltage applied to the piezoelectric element 11 based on the output control signal sent from the controller 33. Thereby, in synchronization with the waveform of the pulsation cycle pulse, ultrasonic energy having an intensity inversely proportional to the level of the temperature detection signal one cycle before the pulsation is emitted from the piezoelectric element 11.
In addition, as shown in FIG. 8, the ultrasonic energy treatment method according to the present embodiment is a temporal change of a loss value due to blood flow of ultrasonic energy emitted in the energy injection step (step SC5), that is, a temperature sensor. 13 includes a temperature detection step (step SA1, loss value detection step) for detecting the temperature of 13 and a pulsation cycle detection step (step SC2) for detecting the pulsation cycle of the blood flow.
In the energy injection process, in synchronization with the waveform of the pulsation period detected in the pulsation period detection process, when the temperature detected by the temperature sensor 13 detected in the temperature detection process rises, the intensity of the ultrasonic energy is lowered to measure the energy. When the temperature detected by the temperature sensor 13 decreases, the intensity of the ultrasonic energy is increased.
The operation of the ultrasonic energy therapy apparatus 200 and the ultrasonic energy therapy method configured as described above will be described with reference to the flowchart of FIG.
In order to treat a lesioned part of a patient by the ultrasonic energy treatment apparatus 200 and the ultrasonic energy treatment method according to the present embodiment, the temperature sensor 13 is energized to insert the insertion part 1 into the patient's blood vessel, and the balloon 19 Thus, the insertion portion 1 is fixed in the positioning state.
The temperature of the temperature sensor 13 is detected by the temperature detector 25 (step SA1, temperature detection step), and a temperature detection signal is sent to the pulsation cycle detector 41 and the A / D converter 43. In the pulsation cycle detection unit 41, the temperature detection signal is compared by the comparator 47, and a pulsation synchronization pulse is generated and sent to the control unit 33 (step SC2, pulsation cycle detection step).
In addition, the temperature detection signal is AD converted by the A / D conversion unit 43, and the temperature detection signal for one cycle of the nth pulsation is stored in time series in the FIFO memory 45 (step SC3).
Next, in the pulsation n + 1 period (step SC4 “Yes”), the control unit 33 reads the temperature detection signal for one pulsation period stored in the FIFO memory 45 from the oldest in chronological order.
Then, the control unit 33 synchronizes with the waveform of the (n + 1) th pulsation cycle pulse sent from the pulsation cycle detection unit 41 based on the temperature detection signal for the nth one cycle read from the FIFO memory 45, and n An output control signal for injecting ultrasonic energy having an intensity inversely proportional to the level of the temperature detection signal at the time of the pulsation is sent to the amplifying unit 23.
Specifically, in synchronization with the waveform of the (n + 1) th pulsation cycle pulse, an ultrasonic wave is detected when the temperature detected by the temperature sensor 13 is increased so that a desired amount of ultrasonic energy is irradiated onto the living tissue. When the energy intensity is lowered and the temperature detected by the temperature sensor 13 is lowered, an output control signal for increasing the intensity of the ultrasonic energy is sent to the amplifying unit 23.
In the amplification unit 23, the amplification factor of the voltage applied to the piezoelectric element 11 changes based on the output control signal sent from the control unit 33. Thereby, in synchronization with the waveform of the (n + 1) th pulsation period pulse, when the temperature detection signal of the temperature sensor 13 rises, ultrasonic energy is emitted from the piezoelectric element 11 with a weak intensity, and the temperature sensor 13 detects the temperature. When the signal falls, ultrasonic energy is emitted from the piezoelectric element 11 with a strong intensity (step SC5, energy injection process). That is, the output of ultrasonic energy emitted in synchronization with the waveform of the (n + 1) th pulsation cycle pulse corresponds to 1 / (temperature detection signal at the nth pulsation).
When the irradiation of the (n + 1) th ultrasonic energy is completed, the temperature detection signal for one cycle of the nth pulsation stored in the FIFO memory 45 is initialized (step SC6). Then, n is counted up (step SC7), and the process returns to step SC3.
Here, the amount and speed of blood flow change greatly due to the pulsation, the blood flow is the fastest during the pulsation systole, and the blood flow is almost zero during the diffusion phase of the pulsation. For this reason, as shown in FIG. 9, the temperature detection signal (loss amount of ultrasonic energy) of the temperature measuring sensor 13 detected by the temperature detection unit 25 also periodically changes with the periodic change of pulsation. FIG. 9 shows changes in blood flow in the vicinity of the temperature sensor 13, the detected temperature of the temperature sensor 13, the output signal of the comparator 47, the pulsation cycle pulse, and the output of ultrasonic energy.
According to the ultrasonic energy treatment apparatus 200 and the ultrasonic energy treatment method according to the present embodiment, as shown in FIG. 9, a desired amount of ultrasonic energy is applied to the living tissue in synchronization with the waveform of the pulsation cycle pulse. By changing the intensity of the ultrasonic energy emitted from the piezoelectric element 11 in inverse proportion to the level of the temperature detection signal one cycle before the pulsation so as to be irradiated, it is possible to prevent excessive irradiation or insufficient irradiation of ultrasonic energy. .
Next, an ultrasonic energy treatment apparatus and an ultrasonic energy treatment method according to the third embodiment of the present invention will be described.
As shown in FIG. 10, the ultrasonic energy treatment apparatus 300 according to the present embodiment is different from the first embodiment in that the insertion portion 1 includes two temperature measuring sensors 13A and 13B.
The two temperature measuring sensors 13 </ b> A and 13 </ b> B are spaced apart from each other in the longitudinal direction of the insertion portion 1. The temperature sensor 13A is disposed closer to the proximal end side of the insertion portion 1 than the piezoelectric element 11, and the temperature sensor 13B is disposed closer to the distal end side of the insertion portion 1 than the piezoelectric element 11. A piezoelectric element 11 is arranged in the middle. The temperature measuring sensors 13A and 13B are connected to the main body 3 by signal lines 17A and 17B.
As shown in FIGS. 11 and 12, the main body 3 includes a temperature detector 25A that detects the temperature of the temperature sensor 13A, a temperature detector 25B that detects the temperature of the temperature sensor 13B, and a temperature detector 25A. A pulsation cycle detection unit 41A for sampling the temperature detection signal, a pulsation cycle detection unit 41B for sampling the temperature detection signal from the temperature detection unit 25B, and the phase and timing of the pulsation cycle pulses output from these pulsation cycle detection units 41A and 41B Temperature sensor 13A, 13B, upstream temperature sensor determination unit 51 for determining which one is located upstream of blood flow, and the temperature sensor from the phase and timing of pulsation cycle pulses of pulsation cycle detection units 41A, 41B And a time measuring unit 53 that measures the time lag of the temperature change of 13A and 13B.
The pulsation cycle detection units 41A and 41B generate pulsation synchronization pulses indicating the pulsation cycle based on the temperature detection signals from the sampled temperature detection units 25A and 25B. The blood flow changes greatly due to the pulsation, and the temperature of the temperature measuring sensors 13A and 13B changes accordingly. Since these temperature measuring sensors 13A and 13B are spaced apart from each other, as shown in FIG. 13, a time lag occurs in the temperature change detected by the temperature measuring sensors 13A and 13B. This time lag can be measured based on the phase and timing of the pulsation synchronization pulses of the pulsation cycle detectors 41A and 41B.
The main body 3 also includes an A / D converter 43A that AD converts the temperature detection signal output from the temperature detector 25A, and an A / D converter 43B that AD converts the temperature detection signal output from the temperature detector 25B. And the FIFO memory 45A for temporarily storing the temperature detection signal AD-converted by the A / D conversion unit 43A for each pulsation in chronological order and the temperature detection signal AD-converted by the A / D conversion unit 43B. A FIFO memory 45B that temporarily stores pulsation for one cycle in sequence order, and temperature detection signals of the temperature sensors 13A and 13B determined to be arranged upstream by the upstream temperature sensor determination unit 51 are used as the FIFO memory 45A. , 45B, and a selector 55 that selectively reads the data from the data and sends it to the control unit 33.
The control unit 33 generates an output control signal for emitting ultrasonic energy having an intensity inversely proportional to the level of the temperature detection signal of the temperature sensor 13A or the temperature sensor 13B sent from the selector 55. Specifically, the controller 33 increases the temperature of the temperature sensor 13A or the temperature sensor 13B so that a desired amount of ultrasonic energy is irradiated onto the living tissue, that is, the ultrasonic energy. If the loss amount of the ultrasonic energy is reduced, the intensity of the ultrasonic energy is lowered, and if the temperature detected by the temperature sensor 13 is lowered, that is, if the loss amount of the ultrasonic energy is increased, the intensity of the ultrasonic energy is raised. An output control signal is sent to the amplifying unit 23.
Further, the control unit 33 adjusts the timing at which the amplification unit 23 changes the voltage amplification factor based on the time lag information sent from the time measurement unit 53. For example, if the time lag of temperature change of the temperature measuring sensors 13A and 13B is X [msec], the control unit 33 is based on the temperature detected by the temperature measuring sensor 13A or the temperature measuring sensor 13B arranged on the upstream side of the blood flow. As shown in FIGS. 14 and 15, the amplification unit 23 sets the amplification factor by delaying the timing by X / 2 [msec] after the pulsation synchronization pulse of the pulsation cycle detection unit 41A or the pulsation cycle detection unit 41B changes. It is supposed to be changed.
As a result, as shown in FIGS. 14 and 15, the flow velocity detection position in the blood where the flow velocity is detected is shifted by a time delay until reaching the irradiation position of the ultrasonic energy emitted from the piezoelectric element 11, The intensity of the ultrasonic energy emitted from the piezoelectric element 11 is changed. 14 and 15 show the temperature detected by the temperature sensor 13A, the temperature detected by the temperature sensor 13B, the output of the pulsation cycle detector 41A, the output of the pulsation cycle detector 41B, and the difference time between the pulsation cycle detectors 41A and 41B. The relationship between the signal, the pulsation cycle pulse and the output of the ultrasonic energy is shown. FIG. 14 is an example of a timing chart when the temperature sensor 13 is arranged upstream in the blood flow direction. FIG. 15 shows a case where the temperature sensor 13 is arranged upstream in the blood flow direction. It is an example of a timing chart.
Further, in the ultrasonic energy treatment method according to the present embodiment, as shown in FIG. 16, the temperature detection step (step SA1, loss value detection step) is more than the irradiation position of the ultrasonic energy emitted by the energy emission step. Temporal change in the loss value of ultrasonic energy based on the blood flow velocity obtained by detection upstream in the blood flow direction, that is, the temperature of the temperature sensor 13A or the temperature sensor 13B arranged upstream in the blood flow direction. Is supposed to be detected.
The energy injection process (step SD5) is a time delay until the flow velocity detection position in the blood whose temperature is detected by the temperature detection process reaches the irradiation position of the ultrasonic energy emitted by the energy injection process, that is, The emission of ultrasonic energy is adjusted by shifting the timing by about half the time lag of the temperature change of the temperature measuring sensors 13A and 13B measured by the time measuring unit 53.
The operation of the ultrasonic energy treatment apparatus 300 and the ultrasonic energy treatment method configured as described above will be described with reference to the flowchart of FIG.
In order to treat a patient's lesion by the ultrasonic energy treatment apparatus 300 and the ultrasonic energy treatment method according to the present embodiment, the temperature sensor 13A, 13B is energized to insert the insertion portion 1 into the patient's blood vessel. The insertion portion 1 is fixed in a positioning state by the balloon 19.
The temperature detectors 25A and 25B detect the temperatures of the temperature measuring sensors 13A and 13B (step SA1), and the temperature detection signals are sent to the A / D converters 43A and 43B and the pulsation cycle detectors 41A and 41B. The temperature detection signals of the temperature detectors 25A and 25B are A / D converted by the A / D converters 43A and 43B, respectively, and stored in the FIFO memories 45A and 45B in chronological order by one pulsation period.
Further, the pulsation cycle detection units 41A and 41B respectively sample the temperature detection signals from the temperature detection units 25A and 25B to generate pulsation cycle pulses, and the pulsation cycle detection unit 51 and the time measurement unit 53 receive the pulsation cycles. A pulse is sent.
In the upstream temperature sensor determination unit 51, the phase and timing of the pulsation cycle pulses from the pulsation cycle detection units 41A and 41B are compared (step SD2). As shown in FIG. 10, when the temperature sensor 13A is disposed upstream of the blood flow than the temperature sensor 13B (step SD2 “Yes”), the controller 33 controls the temperature of the temperature sensor 13A. Based on the change, the amplifying unit 23 is controlled (step SD3).
Specifically, the determination result that the temperature sensor 13A is arranged upstream of the blood flow is sent from the upstream temperature sensor determination unit 51 to the selector 55, and is stored in the FIFO memory 45A by the selector 55. The temperature detection signal for one pulsation period of the temperature sensor 13A is read and sent to the control unit 33 from the oldest in time series order.
The time measurement unit 53 measures the time lag of the temperature change of the temperature measuring sensors 13A and 13B based on the phase and timing of each pulsation cycle pulse from the pulsation cycle detection units 41A and 41B, and controls the time lag information. Sent to the unit 33.
The control unit 33 is inversely proportional to the level of the temperature detection signal so that a desired amount of ultrasonic energy is irradiated to the living tissue based on the temperature detection signal of the temperature measurement sensor 13A sent from the selector 55. An output control signal for injecting an ultrasonic output with high intensity is sent to the amplifying unit 23.
Further, as shown in FIG. 14, the control unit 33, based on the time lag information sent from the time measurement unit 53, only X / 2 [msec] after the pulsation synchronization pulse of the pulsation cycle detection unit 41A changes. The timing for changing the amplification factor of the voltage by the amplifying unit 23 is delayed.
As a result, the temperature sensor 13A is configured so that a desired amount of ultrasonic energy is applied to the living tissue with a delay of X / 2 [msec] after the pulsation synchronization pulse of the pulsation cycle detector 41A changes. When the detected temperature rises, ultrasonic energy is emitted from the piezoelectric element 11 with weak intensity, and when the detected temperature of the temperature sensor 13A falls, ultrasonic energy is emitted with strong intensity (step SD5).
On the other hand, when the temperature sensor 13B is arranged upstream of the blood flow (step SD2 “No”), the control unit 33 controls the amplifier 23 based on the temperature change of the temperature sensor 13B. (Step SD4).
Specifically, the determination result that the temperature sensor 13B is arranged upstream of the blood flow is sent from the upstream temperature sensor determination unit 51 to the selector 55, and is stored in the FIFO memory 45B by the selector 55. The temperature detection signal for one pulsation period of the temperature sensor 13B is read and sent to the control unit 33 from the oldest in chronological order.
The control unit 33 is inversely proportional to the level of the temperature detection signal so that a desired amount of ultrasonic energy is irradiated to the living tissue based on the temperature detection signal of the temperature measurement sensor 13B sent from the selector 55. An output control signal for injecting an ultrasonic output with high intensity is sent to the amplifying unit 23.
In addition, as shown in FIG. 15, the control unit 33, based on the time lag information sent from the time measurement unit 53, only changes X / 2 [msec] after the pulsation synchronization pulse of the pulsation cycle detection unit 41B changes. The timing for changing the amplification factor of the voltage by the amplifying unit 23 is delayed.
Accordingly, the temperature sensor 13 is configured so that a desired amount of ultrasonic energy is irradiated to the living tissue with a delay of X / 2 [msec] after the pulsation synchronization pulse of the pulsation period detection unit 41B changes. When the detected temperature rises, ultrasonic energy is emitted from the piezoelectric element 11 with a weak intensity, and when the temperature detected by the temperature sensor 13 falls, the ultrasonic energy is emitted with a strong intensity (step SD5).
As described above, according to the ultrasonic energy treatment apparatus 300 and the ultrasonic energy treatment method according to the present embodiment, the amount and speed of the blood flow change according to the pulsation timing and the state of the patient. Along with the change, the amount of thermal energy carried away by the blood flow in the ultrasonic energy also changes, but the piezoelectric element 11 is controlled at a timing corresponding to the actual change in the blood flow, and excessive irradiation or insufficient irradiation of the ultrasonic energy Can be prevented.
In the said 2nd Embodiment and 3rd Embodiment, while the control part 33 controlled the intensity | strength of the ultrasonic energy from the piezoelectric element 11, it decided that the energy injection | emission process adjusted the intensity | strength of ultrasonic energy. Instead of this, the control unit 33 may control the emission time of ultrasonic energy generated from the piezoelectric element 11 so that a desired amount of ultrasonic energy is irradiated to the living tissue. Further, the energy injection step may adjust the emission time of the ultrasonic energy so that a desired amount of ultrasonic energy is irradiated to the living tissue.
In the first to third embodiments, the temperature sensors 13, 13A and 13B are adopted as means for detecting the blood flow velocity. Instead of this, for example, by ultrasonic waves. An ultrasonic Doppler that measures the blood flow rate may be employed. As a means for detecting the blood flow velocity, Karman vortex flow velocity sensors 57A, 57B, etc. may be employed instead of the temperature measuring sensors 13, 13A, 13B as shown in FIG.
The embodiment of the present invention has been described in detail with reference to the drawings. However, the specific configuration is not limited to this embodiment, and includes design changes and the like within a scope not departing from the gist of the present invention. For example, the present invention is not limited to those applied to the above-described embodiments and modifications, but may be applied to embodiments in which these embodiments and modifications are appropriately combined, and is not particularly limited. .
1 Insertion Section 11 Piezoelectric Element (Energy Injection Section)
13, 13A, 13B Temperature sensor (energy loss measurement unit)
25, 25A, 25B Temperature detection unit (energy loss measurement unit)
31 Comparison part 33 Control part 41 Pulsation period detection part 100,200,300 Ultrasonic energy treatment apparatus SA1 Temperature detection process (loss amount measurement process, loss value detection process)
SA2, SA5 Comparison process SA4, SC5, SD5 Energy irradiation process SC2 Pulsation cycle detection process
An insertion portion having an elongated shape that can be inserted into a blood vessel;
An energy emitting unit that is attached to the insertion unit and emits ultrasonic energy from inside the blood vessel to a living tissue outside the blood vessel;
A loss amount measuring unit for measuring a loss amount due to blood flow of ultrasonic energy emitted from the energy emitting unit;
A control unit that controls the energy emitting unit in accordance with a loss amount measured by the loss amount measuring unit so that a desired amount of the ultrasonic energy is irradiated to the living tissue ;
A comparison unit that compares the loss amount measured by the loss amount measurement unit with a predetermined first threshold ;
When the control unit determines that the loss amount exceeds the predetermined first threshold, the control unit increases the intensity of the ultrasonic energy and / or lengthens the injection time, and the loss amount is given if it is determined that the first threshold value or lower the intensity of ultrasound energy down and / or injection time you short ultrasonic energy treatment device.
A pulsation cycle detection unit for detecting a pulsation cycle of blood flow ,
The controller reduces the intensity of the ultrasonic energy when the loss measured by the loss measurement unit decreases in synchronization with the waveform of the pulsation cycle detected by the pulsation cycle detection unit and / or or injection time was short, measured the amount of loss if the increased raised intensity of the ultrasound energy and / or you longer injection time ultrasonic energy treatment device.
A control unit that controls the energy emitting unit according to a loss amount measured by the loss amount measurement unit so that a desired amount of the ultrasonic energy is irradiated to the living tissue ;
The loss amount measurement unit measures the loss amount based on the blood flow velocity obtained by detecting upstream of the irradiation position of the ultrasonic energy emitted by the energy emission unit in the blood flow direction,
The control unit shifts the timing by a time delay until the flow velocity detection position in the blood where the flow velocity is detected by the loss amount measurement unit reaches the irradiation position of the ultrasonic energy emitted from the energy emission unit. that controls the energy emitting portion Te ultrasonic energy treatment device.
When the comparison unit determines that the loss amount is equal to or less than the predetermined first threshold value, the comparison unit compares the loss amount with a predetermined second threshold value that is smaller than the predetermined first threshold value;
When the loss by the comparison unit is less than or equal to the predetermined second threshold value, the ultrasonic energy treatment device of claim 1, wherein the control unit stops the radiation of the ultrasonic energy.
JP2014147802A 2014-07-18 2014-07-18 Ultrasonic energy treatment device Active JP6342247B2 (en)
JP2014147802A JP6342247B2 (en) 2014-07-18 2014-07-18 Ultrasonic energy treatment device
PCT/JP2015/057255 WO2016009672A1 (en) 2014-07-18 2015-03-12 Device for ultrasonic energy therapy and method for ultrasonic energy therapy
DE112015002926.5T DE112015002926T5 (en) 2014-07-18 2015-03-12 Apparatus for ultrasonic energy therapy and method for ultrasound energy therapy
CN201580039791.1A CN106659529A (en) 2014-07-18 2015-03-12 Device for ultrasonic energy therapy and method for ultrasonic energy therapy
US15/401,464 US20170113069A1 (en) 2014-07-18 2017-01-09 Ultrasonic energy therapy device and ultrasonic energy therapy method
JP2016022135A JP2016022135A (en) 2016-02-08
JP6342247B2 true JP6342247B2 (en) 2018-06-13
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JP2014147802A Active JP6342247B2 (en) 2014-07-18 2014-07-18 Ultrasonic energy treatment device
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JP (1) JP6342247B2 (en)
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DE (1) DE112015002926T5 (en)
WO (1) WO2016009672A1 (en)
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