JPH02277462A - Body embedding type liquid injection pump device - Google Patents

Abstract

PURPOSE:To provide safety high enough to secure good liquid feed action over a long period of time by providing a vibration means vibrating the flow passage part of one of or both of a reservoir and a liquid feed catheter and the drive means thereof. CONSTITUTION:When AC voltage of certain voltage and frequency is applied to the piezoelectric vibrator 9 of a pump 4 to drive the same, a medical fluid flows in the order of a reservoir 3, a pump chamber 10 and a catheter 2 to be injected in a blood vessel. At this time, when AC voltage is preliminarily applied to a piezoelectric electrode 17 to vibrate the catheter 7, a cyclical pressure change is generated in the vicinity of the wall surface of the catheter 2 and, when a pressure change is imparted at a proper cycle with proper intensity, the diffusion speed of medium particles increases. Therefore, drug particles are always diffused in the vicinity of the wall surface of the catheter 2 by diffusion speed increase action. As a result, even when the drug particles are adhered to the catheter, they are soon separated therefrom. No adhesion of the drug particles to the wall surface of a flow passage is generated.

Description

DETAILED DESCRIPTION OF THE INVENTION [Field of Industrial Application] The present invention relates to an implantable infusion pump device that is implanted in a living body to administer a medicinal solution.

[Prior Art] As seen in Japanese Patent Application Laid-Open No. 59-32463, an implantable infusion pump device is known which is implanted in a living body to administer a medicinal solution. This pump device is used by being implanted subcutaneously for the purpose of controlling blood sugar levels in diabetic patients and continuously administering anticancer drugs to cancer patients. In addition to the pump section, this device is provided with a reservoir for storing the medicinal solution, a catheter for delivering the medicinal solution, and the like.

[Problems to be Solved by the Invention] However, if this pump device is used for a long period of time, there is a risk that the drug may adhere to the reservoir or the wall of the channel of the catheter, etc., causing blockage of the channel. . For example, when the purpose is to control blood sugar levels, if insulin adheres to the wall of the channel, the pump will no longer be able to effectively deliver the fluid.

That is, there was a problem in that insulin could not be administered appropriately, which had a serious adverse effect on patients using the insulin. The same situation applies when using it for other purposes.

The present invention has been made with attention to the above-mentioned problems, and its purpose is to provide a means for preventing drug adhesion in the flow path from the reservoir to the tip of the injection catheter, thereby ensuring good liquid delivery over a long period of time. It is an object of the present invention to provide a highly safe implantable liquid injection pump device that can ensure its effectiveness.

[Means and effects for solving the problems] In order to solve the above problems, the present invention vibrates the flow path section from the reservoir to the tip of the catheter to prevent the drug from adhering to the inner wall surface of the flow path. This ensures good liquid feeding action over the entire period.

Embodiment FIGS. 1 to 12 show a first embodiment of the present invention. This implantable liquid injection pump device 1 is constructed as shown in FIGS. 1 to 9. That is, the indwelling main body part 1a and the infusion catheter 2 connected thereto.
A bag-shaped reservoir 3 for storing a medicinal solution and a liquid feeding pump 4 are incorporated in the indwelling main body 1a. The reservoir 3, the liquid-feeding pump 4, and the catheter 2 are sequentially connected to form a flow path, and the medicinal liquid is supplied into the injection site, for example, a blood vessel 74.

The reservoir 3 is made of an elastic polymer membrane such as Sl so that the volume changes depending on the amount of the stored chemical solution. In the middle of the flow path from the reservoir 3 to the pump 4, a punctureable septum 5 made of an elastic material such as St is provided to enable percutaneous replenishment of the drug solution. A needle stopper 7 is attached to the lower part of the septum 5 via a coil spring 6.

As shown in FIGS. 6a and 6b, this needle stopper 7 is formed into a disk shape with an upright peripheral edge, and has a communication opening 8 cut out in a portion facing the reservoir 3 side. This needle stopper 7 is normally pulled up toward the septum 5 by a coil spring 6, as shown in FIGS. 1 and 4, and is retracted from the liquid feeding flow path so that the medicinal solution can be fed. Then, as shown in FIG. 5, when the injection needle 75 of the syringe barrel 76 is inserted into the septum 5, the injection needle 75 pushes down the needle stopper 7 against the elastic urging force of the coil spring 6.

The needle stopper 7 blocks the liquid feeding flow path and communicates with the reservoir 3 through the communication opening 8.

Thus, it is possible to fill only the reservoir 3 with the chemical solution while blocking the flow path on the side of the liquid feeding pump 4.

The pump 4 also has a pump chamber 10 communicating with the liquid feeding channel.
A membrane-shaped piezoelectric vibrator 9 made of bimorph is installed opposite to the flow path side, and check valves 11 are provided on the inflow side and the outflow side of the pump chamber 10, respectively. Each check valve 11 is provided so that the chemical solution flows only to the delivery side. An elastic membrane 12 and a communication hole 13 are provided on the opposite side of the piezoelectric vibrator 9 from the pump chamber 10 . Then, the liquid is sent to the catheter 2 side through the check valve 11 by the pressure difference between the inside and outside caused by the pressure vibration in the pump chamber 10 caused by driving the piezoelectric vibrator 9.

The catheter 2 is connected via a cap 14 provided on the indwelling main body 1a, and communicates with the pump 4. This catheter 2 is constructed as shown in FIG. That is, the piezoelectric wire 1 is coiled inside the tube body 2a.
7 is buried from the base 14 side to just in front of the tip 18. This piezoelectric wire 17 constitutes a vibrating section 25, which is a vibrating means for vibrating the catheter 2. As shown in FIG.
9. It has a three-layer structure consisting of a piezoelectric rubber 20 and an outer electrode 21. The core wire 19 is made of a thin metal wire to serve as an electrode, and the piezoelectric rubber 20 is formed by encircling a large number of piezoelectric fine particles 22 of piezoelectric ceramic such as PZT into a polymer rubber 23, as shown in FIG. This is what I did. In this case, the piezoelectric particles 22 are set to be polarized in the radial direction of the electric wire 17. The outer electrode 21 is formed of a metal mesh or vapor-deposited metal.

Therefore, the core wire 19 of this piezoelectric wire 17 and the outer electrode 21
When an alternating current voltage is applied between the piezoelectric wire 17 and the piezoelectric wire 17 by a driving means as described later, the piezoelectric fine particles 22 expand and contract in the radial direction of the piezoelectric wire 17 at the voltage frequency. Therefore, the catheter 2 also vibrates at the same frequency.

Incidentally, a protrusion 24 is provided in a collar shape on the distal end portion 18 of the catheter 2 so that the protrusion 24 does not come off when inserted into the blood vessel 74 and left indwelling.

By the way, the piezoelectric vibrator 9 of the pump 4 and the pressure mff1 line 17 embedded in the catheter 2 are connected to the power supply section 26 and control section 27, which are driving means integrated into the indwelling body section 1a, as shown in FIG. Connected as shown. Also,
It is also connected to the energy transmission section 28.

This energy transmission section 28 utilizes the induced electromotive force of the primary coil and the secondary coil, and is designed to be able to charge the power supply section 26 transcutaneously and to also be used for communication with the outside. It is connected to the control section 27.

Further, the pump 4 and the control unit 27 are connected so that an alternating current voltage of an arbitrary frequency and voltage can be applied to the pump 4 to freely change the amount of liquid to be fed. Furthermore, the piezoelectric wire 17 and the control unit 27 connect the catheter 2 so that it can vibrate by continuously applying an alternating current voltage at a desired frequency and voltage between the core wire 19 of the wire 17 and the outer electrode 21. As shown in FIG. 7, the connecting portion between the piezoelectric wire 17 and the control unit 27 is covered with a biocompatible polymer resin 29 made of silicon to prevent exposure, so that it is watertight and does not leak current.

The implantable liquid injection pump device 1 configured as described above is used by being implanted subcutaneously, as shown in FIGS. 11 and 12. The tip of the catheter 2 is placed in a blood vessel 74, for example. In this indwelling state, insulin, anticancer drugs, etc. are injected into the blood vessel 74 continuously or intermittently.

That is, the piezoelectric vibrator 9 of the pump 4 is driven by applying an alternating voltage of a certain voltage and frequency. Then, the medicinal solution flows through the reservoir 3, the pump chamber 10, and the catheter 2 in this order, and is injected into the blood vessel 74. At this time, an AC voltage is applied to the piezoelectric wire 17 to vibrate the catheter 2. Then,
Periodic pressure changes occur near the wall of the catheter 2. Applying pressure changes with appropriate cycles and intensity increases the diffusion rate of medium particles. Therefore, near the wall surface of the catheter 2, drug particles are constantly diffusing due to the effect of increasing the diffusion rate. Therefore, even if drug particles adhere to the catheter 2, they immediately separate. Further, no drug adheres to the wall surface of the channel.

Although the frequency of the voltage applied to the piezoelectric wire 17 may be arbitrarily selected, a frequency between 100 KHz and IMHz is effective. Further, the voltage applied to the pump 4 is suitably in the range of 20 V to 100 V1, and the frequency is suitably in the range of 50 Hz to 150 Hz.

In the catheter 2 in this embodiment, the piezoelectric wire 17 embedded therein is coiled, so the catheter 2 is less likely to be crushed or broken. Therefore, even if the patient using the device twists or bends, the device will not collapse or become obstructed.

Further, since the protrusion 24 is provided on the outer periphery of the distal end portion 18 of the catheter 2, it is difficult to remove it from the blood vessel 74.

Note that FIG. 13 shows a modification of the first embodiment.

That is, this is a catheter 2 in which a coil 30 made of a shape memory alloy is embedded in the distal end 18 of the catheter 2. The memorized shape of this coil 30 is made so that its diameter becomes large.

Usually, as shown in FIG. 14(A), the diameter is small so that it can be easily inserted into the blood vessel 74, and 3.
When the temperature rises to around 5° C., the diameter expands as shown in FIG. 14(B), allowing for secure fixation. Although this modification does not have the protrusion 24, it has the same effect of preventing the protrusion from falling out of the blood vessel 74.

Also, instead of the coil 30 made of a shape memory alloy, the first
As shown in FIG. 5, a crown-shaped shape memory pair 31 may be embedded. This shape memory pair 31 is made of shape memory alloy or shape memory resin. As shown in FIG. 15(A), normally the arms 32 have a cylindrical shape with equal diameter.
When the temperature rises to around 35°C in the blood vessel 74, the arm 32
The diameter of the tip portion 18 is increased by bending so that the portion bulges outward. Therefore, there is an effect similar to that of the above modification.

Furthermore, a pulse voltage may be applied to the piezoelectric wire 17 instead of the alternating current voltage.

Furthermore, the piezoelectric vibrator 9 may be composed of a monomorph,
Alternatively, the elastic diaphragm may be moved by a laminated piezoelectric vibrator.

The biocompatible polymer resin 29 may be other biocompatible materials such as polyurethane.

16 and 17 show a second embodiment of the present invention. That is, the catheter 2 in this embodiment has pressure inside the tube wall of a hollow tube made of polymeric rubber such as Sl.
An electric wire 17 is embedded along the axial direction of the hollow tube. The piezoelectric wire 17 is embedded up to the front end 18 of the catheter 2 as in the above embodiment.

Further, the piezoelectric wires 17 surround the hollow portion of the catheter 2 and are spaced from each other at regular intervals. Note that the number of piezoelectric wires 17 to be buried is arbitrary, but in this embodiment, 3
I have it as a book.

Further, the structure of the piezoelectric wire 17 itself, the connection structure between the piezoelectric wire 17 and the control section 27, etc. are the same as those of the first embodiment.

Therefore, if an alternating current voltage is applied to the piezoelectric wire 17 to vibrate the catheter 2 as in the embodiment III above, periodic pressure changes occur near the wall surface of the catheter 2. When pressure changes are applied with appropriate frequency and intensity,
The diffusion rate of the media particles increases. Therefore, near the wall surface of the catheter 2, drug particles are constantly diffusing due to the effect of increasing the diffusion rate. Therefore, even if drug particles adhere to the catheter 2, they immediately separate. The drug does not adhere to the walls of the channel. 18 to 21 show a third embodiment of the present invention. In this embodiment, the catheter 2 has piezoelectric rings 36 fixed at appropriate intervals around the outer periphery of a hollow tube 35 made of polymeric rubber such as Si. The piezoelectric ring 36 has a donut shape as shown in FIG. 19, and has a three-layer structure consisting of an inner electrode 37, a piezoelectric rubber 20, and an outer electrode 21 in order from the inside as shown in FIG. 21.

The piezoelectric wire 17 of the first embodiment is the same except that the inner electrode 37 is made of a metal mesh or a vapor-deposited metal. The inner electrodes 37 of the piezoelectric ring 36 are connected to each other by an electrode layer 38 made of aluminum foil or the like provided uniformly around the outer circumference of the hollow tube 35, so that they have the same potential. In addition, the outer electrode 21
are connected by a lead wire 39 so as to have the same potential. However, the piezoelectric ring 36 fixed by the base 14 is connected to the control section 27 in the same manner as in the first embodiment. With the above connection, all the piezoelectric rings 36 can be driven at the same timing by the control section 27. The rest is the same as the first embodiment.

Therefore, if an alternating current voltage is applied to the piezoelectric ring 36 to vibrate the catheter, the same effect as in the first embodiment prevents the drug from adhering to the inner wall surface of the catheter 2. Other effects are the same as in the first embodiment.

Note that, instead of the piezoelectric rubber 20, a piezoelectric ceramic such as PZT, which is polarized in the radial direction of the catheter 2, may be used.

22 to 24 show a fourth embodiment of the present invention. This embodiment differs in the configuration of the reservoir 3.

That is, the reservoir 3 is made of elastic polymer rubber such as Si into a bag shape. Furthermore, a coiled piezoelectric wire 17 is embedded in the wall of the reservoir 3. At a fixing part 34 used for fixing the reservoir 3 to the indwelling body part 1a, the piezoelectric wire 17 is not buried in the wall of the reservoir 3 to facilitate fixation.

The inner volume of the reservoir 3 changes depending on the amount of the chemical liquid, and in particular in this embodiment, as shown in FIGS. 22 and 23, the inner volume of the reservoir 3 changes as the coiled piezoelectric wire 17 expands and contracts. change.

The structure of the piezoelectric wire 17, the connection between the piezoelectric wire 17 and the control section 27, etc. are the same as those of the first embodiment.

Therefore, if the reservoir 3 is vibrated by applying an alternating voltage to the piezoelectric wire 17, the chemical solution will not adhere to the inner wall surface of the reservoir 3 in the same manner as in the first embodiment. Furthermore, since the internal volume of the reservoir 3 is changed by the expansion and contraction of the coil portion of the piezoelectric wire 17, its movement is smooth and reliable. Other effects are the same as those of the first embodiment.

Note that the present invention is not limited to the above-mentioned embodiments or their modifications.

C Effects of the Invention] As explained above, according to the present invention, by providing a means for preventing drug adhesion in the flow path from the reservoir to the tip of the injection catheter, it is possible to always ensure good liquid delivery over a long period of time. Safety can be improved.

[Brief explanation of drawings]

1 to 12 show a first embodiment of the present invention,
Figure 1 is a side sectional view of the implantable infusion pump device, Figure 2 is a plan view of the implantable infusion pump device, and Figure 3 is the internal configuration of the implantable infusion pump device. FIG. 4 is a sectional view of the septum section as seen from the reservoir side; FIG. 5 is a sectional view of the septum section during drug replenishment as seen from the reservoir side; FIG. 6a is a diagram of the needle stopper. An external view as seen from the reservoir side, Figure 6b is a sectional view taken along line A-A in Figure 6a,
Figure 7 is a sectional view from the pump to the catheter;
The figure is a perspective view of the piezoelectric wire, Figure 9 is an explanatory diagram of the piezoelectric rubber, Figure 10 is the system configuration diagram, Figure 11 is a sectional view of the implantable infusion pump device in the indwelling state, and Figure 12 is 1 and 13 are perspective views of the indwelling state of the implantable infusion pump device, and FIG. 13 is a sectional view from the pump to the catheter showing a modification of the first embodiment, and FIG. 14 is a perspective view of the catheter of the modification. FIG. 16 is a side sectional view of the catheter portion thereof, FIG. 17 is a sectional view taken along the line B-B in FIG. 16, and FIGS. 18 to 21 are the third embodiment of the present invention. Examples are shown;
Fig. 18 is a side sectional view of the catheter section, Fig. 19 is a sectional view taken along the line C-C in Fig. 18, Fig. 20 is a sectional view taken along the line D-D in Fig. 19, and Fig. 21 is a sectional view taken along the line D-D in Fig. 19. It is an enlarged sectional view of the piezoelectric ring part. 22 to 24 show a fourth embodiment of the present invention, in which FIG. 22 is a side sectional view of the reservoir section in an expanded state, FIG. 23 is a side sectional view of the reservoir section in a deflated state, and FIG. Figure 24 is a cross-sectional view of the reservoir. 1... Implantable infusion pump, 2... Catheter, 3
... Reservoir, 4... Pump, 17... Piezoelectric wire, 20... Piezoelectric rubber, 26... Power supply section, 27...
Control unit, 30... Coil, 36... Piezoelectric ring. Figure 4 Figure 5 Figure 2 Figure 6a Figure 6b Figure 7 Figure 3 Figure 8! i! ! ! [Fig. Fig. Fig. Fig. Fig.] 7 [Fig. ) [Tube body 2a] on page 5, line 18 of the specification
is corrected to "catheter 2". (2) “D-D in Figure 19” on page 16, line 10 of the specification
line" is corrected to "line DD in Fig. 18." (3) Correct box 7, Figure 22, and Figure 23 in the drawing as shown in the attached sheet. Relationship with the person making the amendment Patent applicant (037) Olympus Optical Industry Co., Ltd. 4, Agent 3-7-2 Kasumigaseki, Chiyoda-ku, Tokyo

Claims (1)

[Claims] In an implantable infusion pump device having a configuration in which at least a reservoir for storing a medicinal solution, a liquid-feeding pump part, and a liquid-feeding catheter are connected in order to form a flow path, the reservoir, the liquid-feeding catheter, and An implantable infusion pump device comprising a vibrating means for vibrating one or both of the flow path portions, and a means for driving the vibrating means.