WO2017126676A1 - Drug jet generation device, and drug jet generation method for drug jet generation device - Google Patents

Abstract

Provided is a drug jet generation device capable of spraying a drug at a high speed and delivering the drug to a deep-tissue site while suppressing the thermal degradation of the drug. A drug jet generation device (100, 100b) comprises: a tubular liquid chamber (160); a nozzle (165) formed at an end of the liquid chamber (160); a driving liquid feed device (1) that supplies a driving liquid into the interior of the liquid chamber (160); a drug feed device (5) that supplies a drug in the vicinity of the nozzle (165) on the interior of the liquid chamber (160); a laser light irradiation unit (21) that irradiates the interior of the liquid chamber (160) with pulsed laser light, vaporizes the driving liquid on the interior of the liquid chamber (160), and sprays the drug from the nozzle (165) by means of the driving liquid; and a laser light source (2) that generates pulsed laser light. The liquid chamber (160) comprises a driving liquid introduction port (151) through which the driving liquid supplied from the driving liquid feed device (1) is introduced into the interior of the liquid chamber (160), and a drug introduction port (155) which is positioned further towards the nozzle (165) side than the driving liquid introduction port (151) and through which the drug supplied from the drug feed device (5) is introduced into the interior of the liquid chamber (160). The laser light irradiation unit (21) is disposed between the driving liquid introduction port (151) and the drug introduction port (155).

Description

Drug jet generation device and drug jet generation method of drug jet generation device

The present invention relates to a drug jet generating device and a drug jet generating method of the drug jet generating device.

An optical fiber is inserted into the tube, and a liquid jet (liquid jet) is generated by rapidly heating a liquid such as water filled in the tube by laser light emitted from the laser oscillator through the optical fiber. A surgical instrument (pulse jet knife) that crushes and removes a thrombus or the like by the force of a jet is known (see, for example, Patent Document 1).

Specifically, the laser-induced liquid jet generating device described in Patent Document 1 has a jet generating tube portion that accommodates a laser irradiation portion formed at the tip of an optical fiber and generates a liquid jet. This laser-induced liquid jet generating device has a Y connector and a connecting member that connects the Y connector to a laser oscillator, and the connecting member includes a sleeve member that is screwed with a connecting protrusion protruding from the laser oscillator. The oscillator and the Y connector are detachably connected. An optical fiber is inserted into a predetermined port of the Y connector, and the optical fiber is integrally fixed to the sleeve member by a fixing member such as a resin.

By the way, there are cases where it is desired to administer drugs or the like to a living body. Specifically, there are cases where it is desired to administer anticancer agents, blood coagulation promoters, thrombolytic agents, anticoagulants, vasoconstrictors, etc., genes, cells, regenerative cell drugs, etc. as living drugs during surgery.

As a method for administering a drug, an administration method via a blood vessel, a direct administration method to a target site with a puncture needle (injection needle), and the like are known.

JP 2007-209465 A

However, the administration method using an injection needle via a blood vessel requires a relatively large amount of drug. In addition, since the drug is administered via the blood vessel, an unintended side effect may occur in a portion other than the target site (such as the whole body).

The direct administration method to the target site with a puncture needle allows the drug to be administered locally, and there are few side effects in parts other than the target site. However, in the direct administration method using a puncture needle, there is a risk that the arrival rate of the drug at the target site is relatively small, or the body tissue is damaged by the injection needle.

In addition, for example, in the laser-induced jet generation device described in Patent Document 1, when a drug is simply dissolved in a liquid and the liquid is irradiated with laser light, the drug is thermally deteriorated by irradiation with the laser light. There is a possibility that the drug is diluted and deteriorated by mixing the drug and the liquid.

In addition, for example, when a continuous flow jet in which a liquid is dissolved is injected in a continuous flow jet injection apparatus that injects a continuous flow jet of liquid using a high-pressure pump, a large amount of drug is required. There are problems such as inability to control.

Also, surgery using an endoscope or a microscope has a problem that the surgical field is very narrow and a large surgical instrument cannot be used.

The drug jet generating device of the present invention has at least the following configuration.
A drug jet generating device for jetting a drug,
A cylindrical liquid chamber;
A nozzle formed at an end of the liquid chamber;
A liquid supply device for driving liquid for supplying a liquid for driving into the liquid chamber;
A drug delivery device for supplying a drug near the nozzle in the liquid chamber;
A laser beam irradiation unit configured to irradiate the liquid chamber with a pulsed laser beam, vaporize the driving liquid in the liquid chamber, and eject the medicine from the nozzle through the driving liquid;
A laser light source for generating the pulsed laser light,
The liquid chamber is disposed on the nozzle side of the driving liquid introduction port for introducing the driving liquid supplied from the driving liquid feeding device into the liquid chamber, and for the medicine. A drug introduction port for introducing the drug supplied from the liquid feeding device into the liquid chamber;
The laser light irradiation unit is arranged between the driving liquid introduction port and the drug introduction port.

Moreover, the chemical | medical agent jet production | generation method of the chemical | medical agent jet production | generation apparatus of this invention comprises at least the following structures.
A drug jet generating method of a drug jet generating device for injecting a drug,
The drug jet generator
A cylindrical liquid chamber;
A nozzle formed at an end of the liquid chamber;
A liquid supply device for driving liquid for supplying a liquid for driving into the liquid chamber;
A drug delivery device for supplying a drug to the vicinity of the nozzle in the liquid chamber;
A laser beam irradiation unit configured to irradiate the liquid chamber with a pulsed laser beam, vaporize the driving liquid in the liquid chamber, and eject the medicine from the nozzle through the driving liquid;
A laser light source for generating the pulsed laser light,
The liquid chamber is disposed on the nozzle side of the driving liquid introduction port for introducing the driving liquid supplied from the driving liquid feeding device into the liquid chamber, and for the medicine. A drug introduction port for introducing the drug supplied from the liquid feeding device into the liquid chamber;
The laser beam irradiation unit is disposed between the driving liquid inlet and the drug inlet,
The driving liquid feeding device supplying a driving liquid into the liquid chamber;
The liquid feeding device for medicine supplies a medicine near the nozzle in the liquid chamber;
The laser light irradiation unit irradiating the liquid chamber with pulsed laser light to vaporize the driving liquid in the liquid chamber, and ejecting the medicine from the nozzle through the driving liquid; It is characterized by that.

According to the present invention, it is possible to provide a drug jet generating device that can be locally administered without using a needle and has high efficiency in introducing a drug to a target.
Moreover, according to this invention, the chemical | medical agent jet production | generation apparatus which can inject | pour a chemical | medical agent at high speed and can make a chemical | medical agent reach the deep position of a body tissue can be provided, suppressing the thermal deterioration of a chemical | medical agent.
Moreover, according to this invention, the chemical | medical agent jet production | generation method of a chemical | medical agent jet production | generation apparatus can be provided.

The whole block diagram which shows an example of the chemical | medical agent jet production | generation apparatus which concerns on embodiment of this invention. The elements on larger scale of the chemical | medical agent jet production | generation apparatus shown in FIG. The figure which shows an example of operation | movement of a chemical | medical agent jet production | generation apparatus, (a) is a figure which shows the time at the time of filling with a drive liquid, (b) at the time of chemical | medical agent loading, and (c) when the chemical | medical agent is loaded to a nozzle, respectively. The figure which shows an example of operation | movement of a chemical | medical agent jet production | generation apparatus, (a) is a figure which shows at the time of pulse laser beam irradiation, and (b) at the time of filling with a drive liquid, respectively. Timing chart showing an example of the operation of the drug jet generating device, (a) is a diagram showing the laser light intensity, (b) is a diagram showing the driving liquid delivery amount, (c) is a diagram showing the drug delivery amount, (d) Is a diagram showing the initial jet velocity (jet velocity). The figure which shows an example of the operation | movement of the medicine administration by a medicine jet production | generation apparatus, (a) at the time of non-injection of a medicine, (b) at the time of medicine injection, (c) at the time of medicine arrival to an administration site, (d) The figure which shows the state which the liquid accumulation of the chemical | medical agent produced in the body, (e) is a figure which respectively shows after an injection stop. The figure which shows an example of operation | movement of the chemical | medical agent administration by the injection needle of a comparative example, (a) is the state before inserting the injection needle into the living body, (b) is the state where the injection needle is inserted into the living body, (c) is the drug administration site The state in which the tip of the injection needle has reached, (d) shows the time when the drug is administered, and (e) shows the time when the injection needle is removed. BRIEF DESCRIPTION OF THE DRAWINGS The whole block diagram which shows an example of the chemical | medical agent jet production | generation apparatus (it has a function which adjusts an optical fiber position automatically) which concerns on one Embodiment of this invention. The figure which shows an example of operation | movement of the chemical | medical agent jet production | generation apparatus shown in FIG. 8, (a) is when the distance between a nozzle and a laser beam irradiation part is long, (b) is between a nozzle and a laser beam irradiation part. The figure which respectively shows the case where distance is short. FIG. 8 is a timing chart showing an example of the operation of the medicine jet generating device shown in FIG. 8, (a) shows a laser beam intensity, (b) shows a driving liquid delivery amount, and (c) shows a medicine delivery amount. The figure which shows the position of an optical fiber, and (e) is a figure which shows a jet initial velocity (jet velocity). FIG. 8 is a diagram showing an example of the operation of the medicine jet generating device shown in FIG. 8, (a) before injection, (b) at the first injection, (c) at the first injection stop, and (d) at the first. (E) is a figure which respectively shows the time of the 2nd injection stop at the time of the 2nd injection.

A drug jet generating device (also referred to as a jet generating device) according to an embodiment of the present invention has a light-absorbing liquid (also referred to as a driving liquid or a driving liquid) in a liquid chamber (capillary tube) having a nozzle at an end. ), A liquid chemical (chemical solution) is placed near the nozzle, and the drive liquid in the liquid chamber (capillary tube) is irradiated with laser light to generate vaporized gas. The medicine is ejected from the nozzle so that the liquid is moved toward the nozzle side at high speed and the driving liquid pushes out the medicine.
At the time of laser beam irradiation, the laser beam is absorbed by the liquid and is not irradiated by the drug. For this reason, the chemical | medical agent jet production | generation apparatus can prevent the thermal denaturation and photochemical modification | denaturation of a chemical | medical agent. Further, since the drug jet generating device has a thin tube liquid chamber, the contact area between the driving liquid and the drug is small, and the driving liquid and the drug are difficult to mix.

As a medicine injected by this jet generating device, various medicines, such as an anticancer agent, a blood coagulation promoter, a thrombolytic agent, an anticoagulant, and a vasoconstrictor, are employable, for example. In addition, the solution sprayed by the jet generating device is not limited to the above drugs, and liquid media (liquid therapeutic media, treatments) containing genes, nucleic acids, cells, regenerated cell fluids, radioisotopes, etc. Solution, injection treatment solution, liquid injection substance, etc.).
In the following embodiments, the jet generating device is used at the time of treatment, but is not limited to this form, for example, this jet generating device may be used at the time of diagnosis other than the treatment or under other circumstances, A jet generating device may be used as an auxiliary to some medical action.

Hereinafter, an embodiment of the present invention will be described with reference to the drawings. The embodiment of the present invention includes the contents shown in the drawings, but is not limited to this. In the following description of each drawing, the same parts as those already described are denoted by the same reference numerals, and a part of the overlapping description is omitted.

An example in which the drug jet generating device 100 according to the embodiment of the present invention is applied to a medical instrument such as a jet knife will be described.
As shown in FIG. 1, a drug jet generating device 100 according to an embodiment of the present invention includes a liquid chamber 160, a laser device 2 (laser light source), a driving liquid feeding device 1, a drug feeding device 5, And a control device 4 (control unit). The control device 4 is communicably connected to each component via a wired communication path or a wireless communication path.

As shown in FIGS. 1 and 2, the liquid chamber 160 is configured to hold the liquid F (driving liquid) and the medicine D therein. The liquid chamber 160 may have a grasping part grasped by the operator. The liquid chamber 160 (expansion chamber) is formed in a cylindrical shape. In the present embodiment, the liquid chamber 160 is formed in a cylindrical shape. Specifically, the liquid chamber 160 is formed in a cylindrical shape having an outer diameter Po and an inner diameter Pz. The cylindrical liquid chamber 160 is formed of a material having high strength such as a metal material. Examples of a material for forming the liquid chamber 160 include metals such as stainless steel, titanium, gold, and silver, or materials such as ceramics. In the present embodiment, the inner diameter Pz of the metal thin tube as the liquid chamber 160 is about 0.5 mm to 3.0 mm, preferably about 1.0 mm.

The liquid chamber 160 is connected to the driving liquid feeding device 1 via a tubular member 51 such as a feeding tube. Further, a filter (not shown) may be provided between the tubular member 51 and the liquid chamber 160.

A laser device 2 (laser light source) is connected to one end of the liquid chamber 160 via an optical fiber 22.
The optical fiber 22 is inserted into the liquid chamber 160, and the tip of the optical fiber 22 is disposed at a predetermined position in a metal thin tube that is a cylindrical liquid chamber 160.

The liquid feeding device 1 for driving liquid supplies the liquid F (driving liquid) to the cylindrical liquid chamber 160 such as a metal cylindrical member via the tubular member 51 under the control of the control device 4 (control unit). Examples of the liquid F in the liquid chamber 160 include water, physiological saline, and electrolyte infusion.

Laser device 2 (laser oscillator) as a laser light source generates pulsed laser light under the control of control device 4 (control unit). The pulsed laser light output from the laser device 2 is emitted into the cylindrical liquid chamber 160 from the laser light irradiation unit 21 at the tip of the optical fiber 22 through the optical fiber 22. The laser device 2 can independently control the laser light intensity and the laser light pulse width. Specifically, the control device 4 (control unit) controls the laser device 2 so as to change at least one of the laser energy, the pulse width, and the pulse repetition frequency of the pulsed laser light by the laser light irradiation unit 21.

In the present embodiment, the laser device 2 (laser light source) can irradiate, for example, a pulsed laser beam having a maximum of about 1000 mJ per pulse. Examples of the laser device 2 include a holmium yag laser device (Ho: YAG laser: wavelength 2.1 μm), a thulium yag laser device (Tm: YAG laser: wavelength 2.01 μm), and a thulium fiber laser device (Tm fiber laser: wavelength). 2.01 μm) can be employed. The liquid F such as water, physiological saline, electrolyte infusion, or the like has the energy absorbability of the pulse laser beam from the laser device 2. The laser device 2 is not limited to the laser oscillator.

The drug delivery device 5 supplies the drug D to the cylindrical liquid chamber 160 such as a metal cylindrical member via the tubular member 55 under the control of the control device 4 (control unit). The drug D is, for example, a liquid and desirably has non-absorbability with respect to laser light. As the drug D, for example, various drugs such as anticancer agents, blood coagulation promoters, thrombolytic agents, anticoagulants, vasoconstrictors, genes, cells, and regenerative cell drugs can be employed. The drug D may be a drug in which a powder drug is dissolved in a solution.

An opening-shaped nozzle 165 is formed at the end 160 a of the liquid chamber 160. The nozzle 165 is configured to be able to eject the medicine D injected into the liquid chamber 160 to the outside.

Specifically, as shown in FIG. 2, the diameter Nz of the nozzle 165 is smaller than the inner diameter Pz of the cylindrical liquid chamber 160. The end of the tubular member 55 connected to the drug delivery device 5 is communicated with a drug introduction port 155 provided in the liquid chamber 160 of a metal thin tube. The tubular member 51 connected to the driving liquid delivery device 1 is communicated with a driving liquid inlet 151 provided in a liquid chamber 160 of a metal thin tube.

As shown in FIG. 2, in the liquid chamber 160, the drug chamber 160 </ b> D and the expansion chamber 160 </ b> E are provided in communication between the nozzle 165 and the laser beam irradiation unit 21. The medicine chamber 160D is provided on the nozzle 165 side, and the expansion chamber 160E is provided on the laser light irradiation unit 21 side. The expansion chamber 160E is an area where the generated vaporized gas expands when the driving liquid is irradiated with laser light. The medicine chamber 160D is an area where the medicine D is supplied.
As shown in FIG. 2, the liquid chamber 160 (capillary tube) is provided with a drug introduction port 155 for supplying the drug D to the drug chamber 160D. That is, the medicine introduction port 155 is provided between the nozzle 165 and the driving liquid introduction port 151.
The laser beam irradiation unit 21 is disposed in the liquid chamber 160 between the drug introduction port 155 and the driving liquid introduction port 151. The distance ND between the nozzle 165 and the medicine introduction port 155 is shorter than the distance L1 between the nozzle 165 and the laser beam irradiation unit 21.
The distance LD2 between the drug introduction port 155 and the laser light irradiation unit 21 is shorter than the distance DF between the drug introduction port 155 and the driving liquid introduction port 151.

Specifically, for example, the distance L1 between the nozzle 165 and the laser light irradiation unit 21 is about 50 to 150 mm, and preferably about 100 mm. This distance L1 is set to a distance at which bubbles that are generated and expanded in the liquid chamber 160 by laser light irradiation are not outside the nozzle 165 formed at the end 160a of the liquid chamber 160.

In this embodiment, the inner diameters of the drug chamber 160D and the expansion chamber 160E of the liquid chamber 160 (narrow tube) are about 1 mm, and the cross-sectional area is about 0.785 mm ² . Since the jet flow generation device is configured to eject the drug D within one second from the time when the drug D is introduced into the drug chamber 160D, the jet liquid is transferred from the drug D to the driving liquid F or from the driving liquid F to the drug D. Diffusion is negligible. That is, the jet flow generating device 100 has a structure in which the medicine D and the driving liquid F are not mixed.

A distance LD2 between the drug introduction port 155 and the laser beam irradiation unit 21 is defined as a distance at which the drug D is not thermally deteriorated by the laser beam. When the distance LD2 is relatively short, the drug D is thermally deteriorated by the laser light. When the distance LD2 is relatively long, the amount of the driving liquid F between the medicine D and the laser light irradiation unit 21 increases, and the driving liquid F has a large resistance force. As a result, the driving liquid F is pushed out by the expansion of bubbles. The force is weakened, and the jet velocity of the drug D is reduced.
For this reason, the distance LD2 is defined as a distance at which the drug D is not thermally deteriorated by the laser light and the jet velocity is equal to or higher than a specified value.

As shown in FIG. 2, the optical fiber 22 is inserted into the cylindrical liquid chamber 160 from the end opposite to the nozzle 165. The tip of the optical fiber 22 functions as a laser light irradiation unit 21. The liquid F in the liquid chamber 160 has energy absorbability with respect to the pulsed laser light emitted from the laser light irradiation unit 21. The high laser irradiation unit irradiates the liquid chamber 160 with pulsed laser light to heat and vaporize the liquid F.

The diameter Az of the optical fiber 22 is smaller than the inner diameter Pz of the cylindrical liquid chamber 160. A gap is formed between the optical fiber 22 and the inner surface of the cylindrical liquid chamber 160, and the gap functions as the liquid supply path 140. The liquid F is supplied into the liquid chamber 160 through the liquid supply path 140.

In the example shown in FIG. 2, the optical fiber 22 is inserted into the liquid chamber 160 and a sealing member 169 such as an O-ring and a fixing member 168 disposed at the end 1601 (rear end) of the liquid chamber 160. It is fixed by.

The inner surface of the cylindrical liquid chamber 160 has a mirror surface 160k that reflects the pulsed laser light emitted from the laser light irradiation unit 21. When the pulse laser beam is reflected by the mirror surface 160k, the energy loss of the pulse laser beam is very small.
For this reason, the pulsed laser light emitted from the laser light irradiation unit 21 is reflected directly and once or a plurality of times on the mirror surface 160k on the inner surface of the cylindrical liquid chamber 160, and the boundary surface of the bubble (gas-liquid interface) ).

The boundary surface (gas-liquid interface) between the liquid F and the bubble here refers to the boundary surface (gas-liquid interface) on the opening side (nozzle 165 side) of the cylindrical liquid chamber 160 in the bubbles in the cylindrical liquid chamber 160. ).

The mirror surface 160k is formed on the inner surface of the cylindrical liquid chamber 160 in the vicinity of the laser light irradiation unit 21 at the tip of the optical fiber 22 and in the whole or a part between the laser light irradiation unit 21 and the nozzle 165. Preferably it is formed.

The mirror surface 160k is a surface processed by any one of electrolytic polishing processing, reamer processing processing, plating processing, vapor deposition processing, abrasive spraying processing, and the like. Specifically, when a metal thin tube such as stainless steel or titanium is employed as the cylindrical liquid chamber 160, the mirror surface 160k may be formed by optically polishing the inner surface of the metal thin tube. The mirror surface 160k may be formed by coating the inner surface of the metal thin tube with a material having a high reflectance with respect to the laser wavelength of the pulsed laser light. Specifically, the mirror surface 160k may be formed by coating the inner surface of the metal thin tube with gold or performing gold plating. The mirror surface 160k may be formed by press-fitting a thin thin tube (gold), which is a highly reflective material, into a metal thin tube. Examples of the abrasive spraying process include a process of spraying fine particles (fine resin particles or the like) to which the abrasive is attached into the cylindrical liquid chamber 160 at a high speed.
Moreover, it is preferable that the mirror surface 160k on the inner surface of the liquid chamber 160 has a reflectance of a specified value or more with respect to the pulsed laser light irradiated by the laser light irradiation unit 21.

<Operation of Drug Jet Generation Device 100>
Next, an example of the operation of the drug jet generating device 100 will be described with reference to FIGS. The medicine jet generating device 100 can inject the medicine D at several pulses per second. In the initial state, the drug jet generating device 100 does not irradiate laser light.

First, the inside of the liquid chamber 160 is cleaned by filling the liquid chamber 160 with the new driving liquid F and replacing the old driving liquid F with the new driving liquid F.
Specifically, in step ST1 shown in FIG. 5B, the control device 4 (control unit) controls the driving liquid feeding device 1 so as to fill the liquid chamber 160 with the liquid F (driving liquid). Next, a process of feeding the liquid F is performed. As shown in FIG. 3A, the liquid chamber 160 is filled with the liquid F (driving liquid).

In step ST <b> 2 shown in FIG. 5C, the control device 4 (control unit) controls the drug delivery device 5 to send the set amount DV <b> 1 of drug D to the drug chamber 160 </ b> D of the liquid chamber 160. Perform a liquid treatment. Specifically, as shown in FIG. 3B, the medicine D flows from the medicine feeding device 5 into the medicine chamber 160 </ b> D of the liquid chamber 160 through the tubular member 55 and the medicine introduction port 155.

In step ST3 shown in FIG. 5 (b), the control device 4 (control unit) controls the driving liquid feeding device 1 to feed the liquid F (driving liquid) into the liquid chamber 160. As illustrated in FIG. 3C, the drug D is moved to the nozzle 165 side by the driving liquid F. The control device 4 (control unit) determines the amount of the driving liquid F according to the amount of the medicine D.

In step ST4 shown in FIG. 5A, the control device 4 (control unit) irradiates the laser beam with the laser device 2 based on the set laser energy (laser beam intensity and laser pulse width). I do. In the example shown in FIG. 5A, the laser beam intensity is set to Ia, and the laser pulse width is set to Tla. The laser output (energy) is set to P1 (J) = Ia × Tla.

In ST5 shown in FIG. 5D, a jet of the medicine D is discharged from the nozzle 165 (see FIG. 4A). Specifically, the initial velocity of the jet is Va, and the medicine D is discharged for a predetermined time corresponding to the laser pulse width (Tla). Specifically, the liquid F (driving liquid) in the vicinity of the laser light irradiation unit 21 is heated and vaporized by the pulsed laser light emitted from the laser light irradiation unit 21, and the liquid F is expanded by the expansion of the vaporized gas G (bubbles). The medicine D is pressurized toward the nozzle 165 side, the medicine D is pushed out by the liquid F, and the medicine D is ejected from the nozzle 165.

And when the laser beam intensity of the laser beam irradiation unit 21 becomes zero, the jet velocity of the medicine D decreases and becomes zero.

Then, the liquid chamber 160 is filled with the new driving liquid F, and the old driving liquid F is replaced with the new driving liquid F to clean the liquid chamber 160.
Specifically, in step ST6 shown in FIG. 5B, the control device 4 (control unit) controls the driving liquid feeding device 1 so as to fill the liquid chamber 160 with the liquid F (driving liquid). Next, a process of feeding the liquid F is performed. As shown in FIG. 4B, the liquid chamber 160 is filled with the liquid F (driving liquid).

And in step ST7 shown in FIG.5 (c), the control apparatus 4 (control part) controls the liquid delivery apparatus 5 for chemical | medical agents, and performs the process which liquid-feeds the chemical | medical agent D to the liquid chamber 160. FIG. The medicine D flows into the liquid chamber 160 from the medicine liquid feeding device 5 through the tubular member 55 and the medicine introduction port 155.

In step ST8 shown in FIG. 5 (b), the control device 4 (control unit) controls the driving liquid feeding device 1 to feed the liquid F (driving liquid) to the liquid chamber 160. The drug D moves to the nozzle 165 side by the driving liquid F. The control device 4 (control unit) determines the amount of the driving liquid F according to the amount of the medicine D.

Hereinafter, the drug jet generating apparatus 100 repeats the operations of steps ST4 to ST8 a predetermined number of times at a set frequency based on the set laser beam intensity (power) and the laser beam pulse width. As described above, the medicine jet generating device 100 can inject the pulsed liquid medicine D a predetermined number of times in a short time. The drug jet generating device 100 may spray a single pulsed liquid drug D.

Next, an example of an operation in which the drug jet generating device 100 administers the drug D at a specific depth in the body tissue will be described with reference to FIG.

As shown in FIG. 6 (a), the nozzle 165 of the drug jet generating device 100 is disposed in the vicinity of the administration site of the body tissue 9 when the drug D is not jetted. At this time, the nozzle 165 is arranged so that the injection direction of the medicine D from the nozzle 165 faces the administration site.

As shown in FIG. 6B, the medicine D is ejected from the nozzle 165. The jet of the drug D has a perforating action on the body tissue 9, and a hole is formed from the surface of the body tissue 9 to the inside of the body tissue 9. The depth of the perforations can be controlled by the jet strength.

Then, as the drilling progresses, the kinetic energy of the jet of the drug D decreases, and as shown in FIG. 6 (c), a hole is formed to a depth Z1 corresponding to the strength of the jet. The intensity of the jet is proportional to the output (energy) P1 of the pulse laser beam.

The subsequent jet of the medicine D stays at the bottom position of the hole as shown in FIG.

Then, as shown in FIG. 6 (e), when the irradiation of the laser beam is stopped and the jet of the subsequent medicine D is interrupted, the hole is closed by the internal pressure of the body tissue, and the trace 91 is formed. The The liquid reservoir 8 of the drug D is maintained in that state for a predetermined time and then slowly diffused into the body tissue 9.

In the above-described perforation by the jet of the drug D by the drug jet generating device 100, the pressure of the drug D in the jet (internal pressure of the drug D) is concentrated and diffused in a portion of the body tissue 9 where the mechanical strength is weak. Compared with the case where it is used, the drug D is also diffused during the perforation. For this reason, the drug D can also be diffused into the body tissue 9 in the vicinity of the hole mark 91.

With reference to FIGS. 7 (a) to 7 (e), as an example for comparison, an example of an operation for administering the drug D by the injection needle will be described.
As shown in FIGS. 7A to 7C, the distal end portion of the injection needle N is pierced to the administration site at the deep position of the body tissue 9. During the piercing of the injection needle N, the drug D is not administered. Thereafter, as shown in FIG. 7 (d), the drug D is administered from the tip of the injection needle N. A liquid reservoir 8 'of the drug D is formed at the administration site.

7 (e), when the injection needle N is extracted from the body tissue 9, the hole by the injection needle N is closed by the internal pressure of the body tissue, and a trace 91 'is formed. The liquid reservoir 8 of the drug D is maintained in that state for a predetermined time and then slowly diffused into the body tissue 9. The hole mark 91 'is damaged by the injection needle N, and the healing of the wound is relatively slow.

Furthermore, since the drug D is not administered while the injection needle N is being pierced, the drug D does not diffuse into the body tissue near the trace 91 'through the hole through which the injection needle has passed.

<Pharmaceutical jet generating apparatus 100b>
Next, the medicine jet generating device 100b according to one embodiment of the present invention shown in FIG. 8 will be described. The medicine jet generating device 100b can independently control the injection speed and the injection time of the medicine D injected from the nozzle 165. Further, the medicine jet generation device 100b determines the distance L1, the laser light intensity (power), and the laser light pulse width between the nozzle 165 and the laser light irradiation unit 21 according to the set injection speed and time of the medicine D. And adjusting means for automatically adjusting the timing of introducing the drug D into the liquid chamber and the amount of the drug D, the timing of introducing the driving liquid F into the liquid chamber 160 and the amount of the driving liquid F, and the like.

Specifically, the drug jet generating device 100b includes a liquid chamber 160 (expansion chamber), a laser device 2 (laser light source), a fiber driving device 170, a driving liquid feeding device 1, a drug feeding device 5, and a setting unit 45. , Control device 4b (control unit), and the like. The control device 4b is communicably connected to each component via a wired communication path or a wireless communication path.

The setting unit 45 is configured by an operation input device such as an operation button or a touch panel, and sets the set values of the injection speed (jet initial speed) and the injection time of the medicine D according to the operation of the operator.
The storage unit 46 includes a storage device such as a RAM, a ROM, an HDD, and an SSD. The storage unit 46 stores a table 47, a control program, and the like.

The table 47 of the storage unit 46 includes, for example, a distance L1 between the nozzle 165 and the laser light irradiation unit 21, a set value of the injection speed (jet flow initial speed) and injection time of the medicine D, laser light intensity (power), and laser light. The pulse width, the timing of introducing the drug D into the liquid chamber 160 and the amount of the drug D, the timing of introducing the driving liquid F into the liquid chamber 160 and the amount of the driving liquid F are stored in association with each other in advance.

The control device 4b (control unit) implements the function according to the embodiment of the present invention in the control device (computer) by executing the control program. The control device 4b includes a reading unit 40, an automatic control unit 41, and the like.

The reading unit 40 refers to the table 47 of the storage unit 46, and corresponds to the nozzle 165 and the laser beam irradiation unit 21 corresponding to the setting values of the injection speed (jet flow initial speed) and the injection time of the medicine D set by the setting unit 45. , Information indicating the distance between them, laser light intensity (power) and laser light pulse width, timing of introducing the drug D into the liquid chamber 160 and amount of the drug D, timing of introducing the driving liquid F into the liquid chamber 160 and driving The amount of the liquid F is read from the storage unit 46 regarding the pulse laser beam intensity and the laser beam pulse width.

The automatic control unit 41 of the control device 4b performs a process of outputting to the laser device 2 a laser output control signal corresponding to the information on the pulse laser beam intensity and the laser beam pulse width read from the storage unit 46 by the reading unit 40. Do. Based on the laser output control signal, the laser device 2 outputs a pulse laser beam having a pulse laser beam intensity and a laser beam pulse width at a predetermined timing.

Further, the automatic control unit 41 outputs a fiber drive control signal, which is read from the storage unit 46 by the reading unit 40 and indicates information indicating the distance between the nozzle 165 and the laser light irradiation unit 21, to the fiber drive device 170. Perform the process. The fiber drive device 170 sets the distance between the nozzle 165 and the laser light irradiation unit 21 based on the fiber drive control signal.

Further, the automatic control unit 41 outputs a liquid feeding control signal, which is read from the storage unit 46 by the reading unit 40 and indicates the timing of the driving liquid F and the amount of the driving liquid F, to the driving liquid feeding device 1. I do. The driving liquid feeding device 1 automatically adjusts the timing of introducing the liquid F (driving liquid) from the driving liquid feeding device 1 into the liquid chamber 160 and the amount of the driving liquid F based on the liquid feeding control signal. .

Further, the automatic control unit 41 performs a process of outputting the control signal indicating the timing of the driving liquid F and the amount of the driving liquid F read from the storage unit 46 by the reading unit 40 to the liquid delivery device 5 for medicine. The drug delivery device 5 automatically adjusts the timing of introducing the drug D from the drug delivery device 5 into the liquid chamber 160 and the amount of the drug D based on the control signal.

The fiber driving device 170 sets the distance between the nozzle 165 and the laser light irradiation unit 21 under the control of the control device 4b.

As shown in FIGS. 9A and 9B, the fiber driving device 170 includes an O-ring sealing member 1709 and a fixing member 1603 at the end 1602 (rear end) of the liquid chamber 160. It is fixed. The end 1602 of the liquid chamber 160 and the fixing member 1603 are configured to be screwed together by screwing portions 1602a and 1603a.

The fiber driving device 170 is provided with a motor 1702. As the motor 1702, various motors such as a DC motor and an AC motor can be employed.
A protrusion 1701a provided at the tip of a motor flange 1701, which is a stator of the motor 1702, engages with a fixing member 1603, and has a structure in which the optical fiber 22 penetrating inside is slidably supported.

A rotor 1703 of the motor 1702 has a cylindrical portion extending rearward from the motor flange 1701, and a movable member 1704 and a movable member 1705 that are movable in the axial direction are accommodated inside the cylindrical portion. is doing. A cylindrical movable member 1704 and a movable member 1705 arranged around the optical fiber 22 are screwed together by screwing portions 1704b and 1705a in a state where a sealing member 1708 such as an O-ring is accommodated therein, The optical fiber 22 is supported and fixed.
The cylindrical movable member 1704 has a hole portion through which a guide portion 1701b extending rearward from the motor flange 1701 passes, and is configured to be movable along the guide portion 1701b. In addition, the movable member 1704 and the rotor 1703 of the motor 1702 are screwed together by screwing portions 1704a and 1703a.

Specifically, when the rotor 1703 of the motor 1702 rotates, the cylindrical movable member 1704 and the optical fiber 22 supported by the movable member 1705 are configured to be movable in the axial direction.
That is, the fiber driving device 170 rotates the rotor 1703 of the motor 1702 under the control of the control device 4b, so that the distance between the nozzle 165 and the laser beam irradiation unit 21 provided at the tip of the optical fiber 22 is increased. L1 is configured to be adjustable.

The expansion chamber as the liquid chamber 160 is configured by a thin tube, and the vaporized gas generated by the irradiation of the pulsed laser light expands toward the nozzle 165 from the optical fiber emission point (laser light irradiation unit 21) in the narrow tube. In the operation, the ejection of vaporized gas is dangerous because it is a high temperature and high pressure, and the nozzle 165 side gas-liquid interface (boundary surface FG) needs to stay in the liquid chamber 160 (fine tube) reliably.
Therefore, assuming an expansion volume corresponding to the maximum value of the laser energy (vaporized gas length G1 in the narrow tube corresponding to the maximum expansion volume), the residual liquid length W1 in the liquid chamber 160 (capillary tube) and the optical fiber emission end position (laser) It is necessary to determine and fix the distance L1 between the light irradiation unit 21) (see FIG. 9A).

For example, as shown in FIG. 9B as a comparative example, when the laser energy is reduced (decreased) under this condition, the gap between the nozzle 165 side gas-liquid interface (boundary surface FG) and the laser light irradiation unit 21 is reduced. Is made smaller than G1.
Here, the fluid resistance in the narrow tube is proportional to the contact area (area in the narrow tube) between the liquid F in the liquid chamber 160 (thin tube) and the inner peripheral surface of the narrow tube. On the other hand, the inside area of the narrow tube is proportional to the diameter of the thin tube and the distance between the nozzle 165 and the boundary surface FG. Further, the volume of the liquid F in the narrow tube is proportional to the square of the thin tube radius and the distance between the nozzle 165 and the boundary surface FG. Therefore, when a certain amount of liquid F is to be ejected from the nozzle 165, if the diameter of the thin tube is reduced, the distance between the nozzle 165 and the boundary surface FG must be increased accordingly, and the fluid resistance is increased. turn into. As described above, in order to efficiently generate a jet corresponding to the change of the laser energy, it is necessary to maintain W1 regardless of the laser energy. Therefore, in the chemical | medical agent jet production | generation apparatus which concerns on one Embodiment of this invention, the output point (laser beam irradiation part 21) of the optical fiber 22 is comprised so that a movement is possible according to laser energy (FIG. 9 (a), FIG. 9). (See (b)).

<Operation of Drug Jet Generation Device 100b>
Next, an example of operation | movement of the chemical | medical agent jet production | generation apparatus 100b is demonstrated. In this embodiment, first, the injection speed of the medicine D (initial velocity of the jet) is set to Va, the injection time of the medicine D is set to TDa, and the laser oscillation intensity is set to low (Ia) and laser light as the laser oscillation condition. A case where the pulse width Tl is set to small (Tla) will be described.

According to the injection speed (jet initial speed) of the medicine D set by the setting unit 45 by the operator Va and the injection time TDa of the medicine D, the control device 4b includes the laser device 2, the liquid feeding device 1 for driving liquid (liquid feeding pump). ), A process of controlling the drug delivery device 5 and the fiber driving device 170 is performed.

Specifically, in step ST <b> 11 shown in FIG. 10D, the reading unit 40 of the control device 4 b responds to the injection speed (jet initial speed) of the drug D and the injection time of the drug D set by the setting unit 45. , Information indicating the distance between the nozzle 165 and the laser light irradiation unit 21 corresponding to the injection speed (jet initial speed) of the drug D and the injection time of the drug D from the table 47 stored in the storage unit 46, laser light The intensity (power), the laser light pulse width, the timing of introducing the drug D into the liquid chamber 160 and the amount of the drug D, the timing of introducing the driving liquid F into the liquid chamber 160 and the amount of the driving liquid F are read from the storage unit 46.
The automatic control unit 41 outputs a fiber drive control signal including information indicating the distance L1 between the nozzle 165 and the laser light irradiation unit 21 read from the storage unit 46 by the reading unit 40 to the fiber drive device 170. Process. The fiber driving device 170 automatically adjusts the distance between the nozzle 165 and the laser light irradiation unit 21 so as to be a distance determined based on the setting value and the table by the fiber driving control signal. Specifically, the control device 4b performs a process of moving and fixing the optical fiber emitting end (laser light irradiation unit 21) to the position corresponding to the laser energy by the fiber driving device 170c. That is, the laser beam irradiation unit 21 is set at a distance La from the nozzle 165.

In step ST12 shown in FIG. 10B, the control device 4b performs a process of sending the liquid F to the liquid chamber 160 (expansion chamber) and filling the liquid chamber 160 with the liquid F by the driving liquid feeding device 1. .

In step ST13 shown in FIG. 10 (c), the control device 4b performs a process of sending a predetermined amount of the medicine D set to the liquid chamber 160 by the medicine liquid feeding device 5 (liquid feeding pump).

In step ST14 shown in FIG. 10B, the control device 4b controls the driving liquid feeding device 1 to feed the liquid F (driving liquid) into the liquid chamber 160. The drug D moves to the nozzle 165 side by the driving liquid F. The control device 4 (control unit) determines the amount of the driving liquid F according to the amount of the medicine D.

In step ST15 shown in FIG. 10A, the control device 4b irradiates the laser beam with the laser device 2 so that the set laser energy (laser beam intensity = Ia, laser beam pulse width = Tla) is obtained. I do.

In step ST16 shown in FIG. 10 (e), the jet of the medicine D is emitted from the nozzle 165. Specifically, the drug D is emitted such that the initial jet velocity (jet velocity) is Va and the injection time of the drug D is TDa. Specifically, the liquid F (driving liquid) in the vicinity of the laser light irradiation unit 21 is heated and vaporized by the pulsed laser light emitted from the laser light irradiation unit 21, and the liquid F is expanded by the expansion of the vaporized gas G (bubbles). The medicine D is pressurized toward the nozzle 165 side, the medicine D is pushed out by the liquid F, and the medicine D is ejected from the nozzle 165.

In step ST17 shown in FIG. 10D, the control device 4b emits the optical fiber at a position corresponding to the next laser energy (low laser beam intensity (power) (Ia) × large laser beam pulse width (Tlb)). A process of moving and fixing the end (laser light irradiation unit 21) by the fiber driving device 170 is performed. Specifically, the laser beam irradiation unit 21 is set at a position at a distance Lb from the nozzle 165.

In step ST18 shown in FIG. 10 (b), the control device 4b calculates the pre-injection jet flow rate and the volume change amount accompanying the fiber movement, and the liquid chamber 160 is driven by the liquid supply device 1 (liquid feed pump) for driving liquid. An appropriate amount of the liquid F (driving liquid) is sent to the (expansion chamber), and the liquid chamber 160 is filled with the liquid F (driving liquid).

In step ST19 shown in FIG. 10 (c), the control device 4b performs a process of sending a predetermined amount of medicine D set to the liquid chamber 160 by the medicine liquid delivery device 5 (liquid feed pump).

In step ST20 shown in FIG. 10B, the control device 4b (control unit) controls the driving liquid feeding device 1 to send the liquid F (driving liquid) to the liquid chamber 160. The drug D moves to the nozzle 165 side by the driving liquid F. The control device 4b (control unit) determines the amount of the driving liquid F according to the amount of the medicine D.

Hereinafter, as shown in FIG. 10, the operations of steps ST15 to ST20 are performed as follows. The injection speed of the drug D (initial jet velocity) and the injection time of the drug D, specifically, the injection speed of the drug D is small (Va ) And when the injection time of the medicine D is long (TDb), when the injection speed of the medicine D is high (Vb) and the injection time of the medicine D is short (TDa), the injection speed of the medicine D is high (Vb) and the medicine D When the injection time is long (TDb), it is repeated at the set frequency.

Next, an example of an operation in which the drug jet generating device 100b administers the drug D to specific depths Z1 and Z2 in the body tissue will be described with reference to FIG. However, Z1> Z2.

As shown in FIG. 11A, the nozzle 165 of the drug jet generating device 100b is arranged in the vicinity of the administration site of the body tissue 9 when the drug D is not jetted. At this time, the nozzle 165 is arranged so that the injection direction of the medicine D from the nozzle 165 faces the administration site. A set amount DV1 of the drug D is supplied to the drug room. Pulse laser light is output from the laser light irradiation unit 21. The laser output (energy) is P1. The liquid F (driving liquid) in the vicinity of the laser light irradiation unit 21 is heated and vaporized, the liquid F pressurizes the drug D toward the nozzle 165 due to the expansion of the vaporized gas G (bubbles), and the drug F is pushed out by the liquid F. As shown in FIG. 11B, the medicine D is ejected from the nozzle 165.

A hole is formed from the surface of the body tissue 9 to the inside of the body tissue 9 by the jet of the drug D. The depth of the perforations can be controlled by the jet strength. Then, as the drilling proceeds, the kinetic energy of the jet of the drug D decreases, and a hole is formed to a depth Z1 corresponding to the strength of the jet. The intensity of the jet is proportional to the output (energy) P1 of the pulse laser beam. And the chemical | medical agent D spread | diffuses and the liquid reservoir 8a (8) is formed.

As shown in FIG. 11 (c), when the irradiation of the laser beam is stopped and the jet of the subsequent medicine D is interrupted, the hole is closed by the internal pressure of the body tissue, and a trace 91a (91) is formed. Is done.

Next, the set amount DV2 of the drug D is supplied to the drug room. DV2 <DV1 is set. The driving liquid F is supplied to the liquid chamber 160, and the medicine D is moved to the nozzle side by the driving liquid F. The supply amount of the driving liquid F is determined according to the amount of the medicine D supplied to the medicine chamber 160D.

Then, a pulse laser beam is output from the laser beam irradiation unit 21. The output (energy) of the laser is P2. P2 <P1. The liquid F (driving liquid) in the vicinity of the laser light irradiation unit 21 is heated and vaporized, the liquid F pressurizes the drug D toward the nozzle 165 due to the expansion of the vaporized gas G (bubbles), and the drug F is pushed out by the liquid F. As shown in FIG. 11 (d), the medicine D is ejected from the nozzle 165. A liquid reservoir 8b (8) of the medicine D is formed at a depth Z2 corresponding to the output (energy) P2 of the laser beam. P2 <P1 and Z2 <Z1.

As shown in FIG. 11E, when the irradiation of the laser beam is stopped and the jet of the subsequent medicine D is interrupted, the hole is closed by the internal pressure of the body tissue, and a trace 91b (91) is formed. Is done.

Then, the liquid reservoirs 8 a (8) and 8 b (8) of the drug D are maintained in that state for a predetermined time and then slowly diffused into the body tissue 9.

In the above-described embodiment, the liquid reservoir of the drug D can be easily formed at arbitrary positions with different depths in the body tissue 9.

In the above-described embodiment, the drug jet generating device 100b forms a plurality of liquid pools in the depth direction (Z-axis direction) of the body tissue, but is not limited to this form.
For example, the drug jet generating device arranges a plurality of nozzles one-dimensionally in a predetermined direction (X-axis direction) at a predetermined interval, thereby allowing a predetermined depth of body tissue in the Z-axis direction at a predetermined interval in the X-axis direction. The liquid reservoir of the medicine D can be easily formed at this position.

Further, for example, the medicine jet generating device arranges a plurality of nozzles two-dimensionally at predetermined intervals in the X-axis direction and the Y-axis direction, so that the liquid reservoir of the medicine D is predetermined in the X-axis direction and the Y-axis direction. It is possible to distribute three-dimensionally at predetermined intervals and at predetermined positions in the Z-axis direction (positions having a predetermined depth of the body tissue).

Further, the control device (control unit) of the drug jet generating device can easily define the amount of each drug D formed in the body tissue by controlling the amount of the drug D to be supplied. .

As described above, the drug jet generating devices 100 and 100b according to the embodiment of the present invention include the cylindrical liquid chamber 160 (expansion chamber), the nozzle 165 formed at the end of the liquid chamber 160, and the liquid. The liquid supply device 1 for driving liquid that supplies the driving liquid F (driving liquid) into the chamber 160 via the tubular member 51, and the drug D is supplied to the vicinity of the nozzle 165 in the liquid chamber 160 via the tubular member 55. The liquid delivery device 5 for medicine and the liquid chamber 160 are irradiated with pulsed laser light to vaporize the driving liquid F in the liquid chamber 160, and the medicine D is supplied to the nozzle 165 via the driving liquid F. And a laser light source (laser device 2) that generates pulsed laser light. The liquid chamber 160 is disposed on the nozzle 165 side of the driving liquid introduction port 151 for introducing the driving liquid F supplied from the driving liquid feeding apparatus 1 into the liquid chamber 160, and the driving liquid introduction port 151. A medicine introduction port 155 for introducing the medicine D supplied from the medicine liquid feeding device 5 into the liquid chamber 160 is provided. The laser light irradiation unit 21 is disposed between the drive liquid inlet 151 and the medicine inlet 155.

The driving liquid feeding device 1 supplies the driving liquid F into the liquid chamber 160, the drug feeding device 5 supplies the drug D near the nozzle 165 in the liquid chamber 160, and a laser beam irradiation unit. 21 irradiates the driving liquid F in the liquid chamber 160 (capillary tube) with laser light to generate vaporized gas. Due to the expansion of the vaporized gas, the driving liquid F is moved at high speed toward the nozzle 165 side, and the drug D is ejected from the nozzle 165 so that the driving liquid F pushes out the drug D.

That is, it is possible to provide the drug jet generating devices 100 and 100b that can jet the drug D at a high speed and allow the drug D to reach a deep position in the body tissue.
That is, it is possible to provide the drug jet generating devices 100 and 100b that can be locally administered without using a needle and have high efficiency of drug introduction to the target.
In addition, as described above, the drug jet generating method of the drug jet generating devices 100 and 100b can be provided.

In addition, since the driving liquid F has a wavelength band with good absorbability as the wavelength of the laser light, the laser light is absorbed by the driving liquid F and is not irradiated to the drug D when the laser light is irradiated. Thermal degradation is suppressed.
Further, the heat transfer to the drug D due to the heat conduction during the expansion of the vaporized gas is as short as several milliseconds from the laser irradiation to the jet injection, and therefore, the driving liquid F between the vaporized gas and the drug D is short. It is interrupted by.

Moreover, since the nozzle 165 is formed in the liquid chamber 160 of the thin tube, the drug jet generating devices 100 and 100b according to the embodiment of the present invention can be easily used for an operation using an endoscope or a microscope with a narrow surgical field. Can be used for

In addition, since the drug jet generating devices 100 and 100b according to the embodiment of the present invention have the narrow tube (diameter) liquid chamber 160 (expansion chamber), the drug D and the driving liquid F are not easily mixed. .

In addition, the laser beam irradiation unit 21 of the drug jet generating devices 100 and 100b according to the embodiment of the present invention is disposed between the driving liquid inlet 151 and the drug inlet 155, and with respect to the drug D in the liquid chamber 160. Therefore, it is placed at a position that is not affected by the thermal effect of the pulse laser beam. For this reason, the chemical | medical agent jet production | generation apparatuses 100 and 100b which can further reduce the thermal deterioration of the chemical | medical agent D can be provided.

Moreover, the laser apparatus 2 (laser light source) of the chemical | medical agent jet production | generation apparatus 100b which concerns on embodiment of this invention controls a laser beam intensity and a laser beam pulse width independently by the control apparatus 4b. Further, the medicine jet generating device 100b is configured to set the laser light intensity and the laser light pulse width, and the nozzle 165 and the laser according to one or both of the injection speed and the injection time of the medicine D set by the setting unit 45. Adjustment means (control device 4b, fiber driving device 170) for automatically adjusting the distance to the light irradiation unit 21 is provided.
For this reason, according to the injection speed and injection time of the medicine D set by the setting unit 45, the medicine jet generating device 100b that can inject the medicine D can be provided.

In addition, the drug jet generation devices 100 and 100b according to the embodiment of the present invention optimally adjust the injection speed of the drug D, so that the difference in composition of body tissues (difference in elastic modulus, coupling rate between body tissues The drug D can selectively reach a deep position (about 1 mm to 20 cm) of the body tissue without damaging the necessary body tissue.

Further, the drug jet generating devices 100 and 100b according to the embodiment of the present invention can jet the drug D from the nozzle continuously in a short time in a pulse shape. For example, by injecting a plurality of times toward the deep part of the body tissue in a short time, the drug D can easily reach a deep position of the body tissue as compared with a case of single injection.

In addition, the drug jet generating devices 100 and 100b according to the embodiment of the present invention include the above-described drug jet mode for jetting the drug D and the liquid jet mode (the liquid jet without filling the drug chamber 160 with the drug D). And a mode for performing an operation such as an incision). In this case, the control part of the chemical | medical agent jet production | generation apparatuses 100 and 100b 4 adjusts the position of the laser beam irradiation part 21 automatically according to chemical | medical agent injection mode and liquid injection mode.

The drug jet generating devices 100 and 100b according to the embodiment of the present invention may have a suction device. Specifically, for example, the drug jet generation devices 100 and 100b may have suction pipes provided coaxially on the outer peripheral side of the cylindrical liquid chamber 160. The drug jet generating devices 100 and 100b can suck the extra drug D and liquid F (driving liquid) with a suction device as necessary.

Further, the drug jet generating device according to the present invention may be applied to a medical device such as a surgical operation robot. This surgery support robot includes an arm equipped with a drug jet generation device and an endoscope camera, and is configured to perform a predetermined surgery by remote operation by an operator's operation device.

As described above, the embodiments of the present invention have been described in detail with reference to the drawings. However, the specific configuration is not limited to these embodiments, and there are design changes and the like without departing from the gist of the present invention. Is included in the present invention.
Further, the embodiments described in the above drawings can be combined with each other as long as there is no particular contradiction or problem in the purpose and configuration.
Moreover, the description content of each figure can become independent embodiment, respectively, and embodiment of this invention is not limited to one embodiment which combined each figure.

DESCRIPTION OF SYMBOLS 1 ... Liquid feeding apparatus for drive liquids 2 ... Laser apparatus (Laser light source: Laser oscillator)
4, 4b ... Control device (control unit)
40: Reading unit 41 ... Automatic control unit (adjustment means)
100, 100b ... Drug jet generating device 160 ... Liquid chamber (expansion chamber, thin tube)
165 ... Nozzle 170 ... Fiber drive device (adjustment means)

Claims (4)

1. A drug jet generating device for jetting a drug,
   A cylindrical liquid chamber;
   A nozzle formed at an end of the liquid chamber;
   A liquid supply device for driving liquid for supplying a liquid for driving into the liquid chamber;
   A drug delivery device for supplying a drug near the nozzle in the liquid chamber;
   A laser beam irradiation unit configured to irradiate the liquid chamber with a pulsed laser beam, vaporize the driving liquid in the liquid chamber, and eject the medicine from the nozzle through the driving liquid;
   A laser light source for generating the pulsed laser light,
   The liquid chamber is disposed on the nozzle side of the driving liquid introduction port for introducing the driving liquid supplied from the driving liquid feeding device into the liquid chamber, and for the medicine. A drug introduction port for introducing the drug supplied from the liquid feeding device into the liquid chamber;
   The said laser beam irradiation part is arrange | positioned between the said drive liquid inlet and the said medicine inlet. The chemical | medical agent jet production | generation apparatus characterized by the above-mentioned.
2. The drug jet generating device according to claim 1, wherein the laser beam irradiation unit is disposed at a position where the drug in the liquid chamber is not thermally affected by the pulse laser beam.
3. The laser light source controls laser light intensity and laser light pulse width independently,
   According to one or both of the jetting speed and jetting time of the medicine, the laser beam intensity and the laser beam pulse width, and the adjusting means for automatically adjusting the distance between the nozzle and the laser beam irradiation unit The drug jet generating device according to claim 1 or 2, characterized by.
4. A drug jet generating method of a drug jet generating device for injecting a drug,
   The drug jet generator
   A cylindrical liquid chamber;
   A nozzle formed at an end of the liquid chamber;
   A liquid supply device for driving liquid for supplying a liquid for driving into the liquid chamber;
   A drug delivery device for supplying a drug to the vicinity of the nozzle in the liquid chamber;
   A laser beam irradiation unit configured to irradiate the liquid chamber with a pulsed laser beam, vaporize the driving liquid in the liquid chamber, and eject the medicine from the nozzle through the driving liquid;
   A laser light source for generating the pulsed laser light,
   The liquid chamber is disposed on the nozzle side of the driving liquid introduction port for introducing the driving liquid supplied from the driving liquid feeding device into the liquid chamber, and for the medicine. A drug introduction port for introducing the drug supplied from the liquid feeding device into the liquid chamber;
   The laser beam irradiation unit is disposed between the driving liquid inlet and the drug inlet,
   The driving liquid feeding device supplying a driving liquid into the liquid chamber;
   The liquid feeding device for medicine supplies a medicine near a nozzle in the liquid chamber;
   The laser light irradiation unit irradiating the liquid chamber with pulsed laser light to vaporize the driving liquid in the liquid chamber, and ejecting the medicine from the nozzle through the driving liquid; A drug jet generating method for a drug jet generating device.

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