EP1966782A1

EP1966782A1 - Simulation device for simulating penetration processes

Info

Publication number: EP1966782A1
Application number: EP06828734A
Authority: EP
Inventors: Rainer Burgkart; Robert Riener
Original assignee: Individual
Current assignee: Individual
Priority date: 2005-12-23
Filing date: 2006-12-23
Publication date: 2008-09-10
Also published as: WO2007073733A1; US20090305213A1

Abstract

The invention relates to a simulation device for simulating penetration processes, carried out by a needle- or pin-like instrument or tool, the simulation device comprising: a handle (1), connected to the instrument (2) in a movable manner, the handle (1) being held by an operator, a position determining device (7), which determines the position of the instrument (2) relative to the handle (1) and generates a position signal, a force determining device (6), which determines the force with which the instrument (2) is forced against the body (8) by means of the handle, said force determining device (6) generating a force signal, a controllable actuator for displacement of the instrument (2) relative to the handle (1) and a computing and control unit with a signalling connection to the actuator, said computing and control unit comprising a memory in which penetration information specific to the body and a computer programme are stored and, based on the position and force signals, the actuator is controlled such that on pressing the instrument (2) against the body (8) the same tactile sensation is generated as on handling a real instrument inserted into a real body.

Description

Simulation device for simulating intrusions

The invention relates to a simulation device for simulating penetrations, which are carried out by means of a needle or pen-like instrument or tool, wherein subsequently only the term instrument is used.

For example, in the field of medicine, the introduction of instruments such as needles and catheters into a human or animal body is one of the most common routines in everyday clinical practice. The execution of such routines is in need of exercise because the performer, i. H. the surgeon, without additional aids no visual information about the position of the instrument tip gets, but only on his haptic sensation, d. H. can rely on his tactile sensation.

From the prior art, a variety of injection simulators are known, which are designed for different practice cases, such. For example, from DE 44 14 832 a model for practicing the insertion in blood vessels or from GB 2 288 686 A or WO 03/054834 A1.

Learning the techniques described above with the help of simulators requires that the learner receives a largely realistic overall impression while practicing on the simulator. If, however, this largely realistic overall impression is not achieved by means of the simulator, there is a risk that the learner will be trained incorrectly, so that maladaptation can occur in the implementation of the learned or trained on living patients, which can lead to damage. These damages the patient but should be avoided by the previous practice and training with the simulator.

A particular problem with the so-called haptic simulators, d. H. in simulators with a force feedback, the z. T. heavy and bulky designs of force feedback, which cause the simulation conditions are not similar to the conditions present in living patients.

A particular limitation of the haptic simulators hitherto is the definition of a very narrow work area, where under work area z. B. the body surface of the patient is to understand on the practitioner first select the correct injection site and possibly even by touching with your fingers the injection site must determine very precisely. For training z. B. as a doctor such exercises are essential. In other words, the practitioner not only has to be able to properly guide the instrument after the puncture, but he must also learn to strike the right puncture site.

The known from the prior art haptic, d. H. Injection simulators operating with force feedback do not allow the simulator to be placed on any body at any point, such. B. on the back of a living patient or anywhere an anatomical model made of plastic. The main reason for this is the necessary mechanical connection between the instrument, the practitioner leads by hand and the force-feedback mechanism, which is usually hidden in the anatomical model integrated, resulting in the further disadvantage that this design concept of a haptic injection simulator not for living patient is applicable, the term "injection simulator" is to be understood in the broad sense described above.

In summary, it can thus be stated that the haptic injection simulators known from the prior art have two system-related disadvantages: a. The simulation of the living organism (human, animal) is not possible. b. The learning process of "searching and finding the right puncture site" is also not possible.

In this respect, it is the object of the invention to provide a simulation device that overcomes deficiencies a and b of the prior art.

The problem of overcoming the defect a is achieved with a simulation device according to claim 1. The problem of overcoming the deficiencies a and b is achieved with a simulation device according to claim 5.

The simulation device for simulating penetrations of an instrument into a body has a handle with which the simulation device is manually guided by the operator. The instrument is coupled to the handle so that the instrument is slidable with respect to the handle in a predetermined displacement direction, d. H. When the instrument is pressed against the body, it slides into the handle. This creates for the practitioner and an observer, the visual impression, as if the instrument actually penetrates into the body, although it enters the handle.

It is clear to those skilled in the art that this insertion into the handle by gleichwirkende, d. H. equivalent measures can be replaced. So it is z. B. possible to form the instrument telescopically, d. H. it can, for. B. consist of several pipe sections that are pushed into one another.

Furthermore, a position-determining device is provided which determines the current position of the instrument relative to the handle and generates a current position signal. More specifically, information about the displacement of the instrument tip with respect to the handle must be provided.

Furthermore, a force-determining device is provided, which determines the current force with which the instrument is pressed by means of the handle against the body, wherein the force-determining device generates a current force signal. It is further provided a computer-controlled drive device which causes the instrument can be retracted only against a predetermined force in the handle. This drive device is signal-technically connected to the position-determining device, the force-determining device and the computer.

The drive device is controlled by evaluating the current force and position signal. For this purpose, a computer program is used which simulates the material properties of the body in the form of control signals for the drive device. This relationship will be described in more detail below.

The drive device is either integrated in the handle, or connected from the outside via a coupling device with the handle. As a coupling device z. B. a hydraulic hose suitable.

Below, the control philosophy should be described qualitatively so far that a person skilled in control engineering can build the simulation device.

The aim is to simulate the penetration of a needle into a living part of a human or animal body. It should be simulated that the body portion is covered on its surface with a skin, then z. If, for example, an adipose tissue follows, then a connective tissue layer is to be pierced, followed by a thick muscle tissue and then a solid bone tissue. All of the aforementioned tissue sections of the body are fictitious, i. H. only represented as a software model in the calculator.

Since the simulation serves the purpose of practicing a penetration action with a hand-guided instrument in a real body, it is expedient and serves the learning success, if the exercise can be performed not only on a model body, but also on a living body. For completeness, therefore, it is mentioned that even if the body portion of a hard Plastic (eg an anatomical model), the haptic effect in the simulation is the same as in a living body part.

When the surgeon presses the simulation device against a living soft body portion, it must be prevented that the needle actually penetrates into the skin, i. H. The needle tip must be such that it can not penetrate the simulation. This is achieved by greatly increasing the area of the needle tip. So it is z. B. possible to attach to the needle tip a small plastic disc.

If the surgeon places the needle with the disc on the skin surface and pushes against the skin, this pressure is determined by the force determination device. If the surgeon presses harder, skin penetration is simulated by the drive device suddenly pushing the needle a little into the handle, d. H. it simulates the penetration of the skin and the underlying fatty tissue, so that then the needle is present at the simulated connective tissue. The drive device allows further insertion of the needle into the handle only when the surgeon presses the needle with the penetration force required in reality against the relatively strong connective tissue. Then comes the muscle tissue, whose penetration is simulated again by a specific retraction of the needle. Now, the needle is on the bone tissue, which can not be penetrated, so that the surgeon feels a stronger resistance, which is achieved by blocking the drive device even with stronger pressures.

For better clarity, a simulation example was chosen in which the needle or another instrument or tool penetrates tissue layers with different strength. It is clear that the same control philosophy can also be used for fabrics and materials which have little or no inhomogeneities. It is also clear that the required forces are not only dependent on the penetration depth, but also on the penetration rate. When resuming a penetration movement, z. B. after discontinuation (stopping the hand movement) can also be required larger forces to overcome the static friction, ie there are so-called "stick-and-slip effect" It will also be apparent to those skilled in the art that the shape and nature of the instrument must also be considered in the simulation software.

The concrete design of the individual components of the simulation device, d. H. the handle, the instrument itself, the mechanical guide of the instrument, the position detecting device, the force detection device and the drive device is selected by the skilled person on the basis of geometrical-constructive requirements that require the training situation, with basic embodiments claimed in the subclaims.

According to claim 2, the drive device is arranged in or on the handle, in which case the part of the drive device is meant, which generates the driving force. It is possible in the handle z. Example, to provide a spindle-nut assembly, wherein the spindle is driven by an electric motor and the nut running on the spindle is firmly connected to the instrument.

According to claim 3, the position detecting device is arranged in or on the handle. It is possible to arrange in the handle an angle sensor so that the rotational movement of the spindle is detected according to claim 2. From the current position of the angle sensor, the current Nadeiposition can be determined.

According to claim 4, the force-determining device is arranged in or on the handle. It is possible to arrange in the handle a force sensor so that the force generated by the handle when pressing the instrument against the body is transmitted to the force sensor. The force sensor is thus to be arranged in a spindle-nut arrangement between the instrument and the spindle nut.

According to claim 5, a position determining device is provided which determines the current spatial position of the instrument relative to the body and generates an electrical position signal, which is supplied to the arithmetic and control unit. Such position determining devices are known in the art as navigation systems, so that only the appropriate application for each case Determine geermittlungsvorrichtung and signal technology to adapt. By this development of the invention, it is z. For example, it is possible to simulate direction-dependent body characteristics, or it can be learned to set up the instrument at the medically correct point on the body surface (eg in the region of the spinal column) and to simulatively pierce the body in the medically correct solid angle.

According to claim 6, a conventional, known in the art optical navigation device is used, wherein on the handle and the body navigation marks are provided, which are recognizable by a camera system for optical navigation.

According to claim 7, the simulation is carried out on a solid model body, such. B. a back portion on which the insertion of the instrument in the area of the spine is practiced. This fixed model body is coupled to a force measuring device which provides electrical measurement signals from which it is possible to calculate at which current point of the model body the instrument tip is placed. This technique is known in the art and z. B. in DE 102 61 673 A1 described in detail.

The invention will be explained in more detail with reference to schematic drawings.

Fig. 1 shows a first embodiment of the invention. Fig. 2 shows a second embodiment of the invention.

Fig. 3 shows a third embodiment of the invention.

Fig. 4 shows a fourth embodiment of the invention.

Fig. 5 shows a first application of the invention.

Fig. 6 shows a second application of the invention. Fig. 7 shows a first application of the invention with navigation system.

Fig. 8 shows a second application of the invention with navigation system.

1 shows as a first embodiment of the invention, the simulation device with a handle 1, with which the device by an operator with the Hand is guided. The instrument is a needle 2, which is connected to the handle 1, wherein the needle 2 with respect to the handle 1 in the direction of the double arrow is slidably formed.

In the handle 1, a spindle-nut assembly 3, 4 is integrated as a drive device, wherein the spindle 3 is driven by a likewise integrated in the handle 1 electric motor 5. The running on the spindle 3 nut 4 is firmly connected via a force sensor 6 to the needle 2. To the electric motor 5, an incremental Winkelmeßsystem 7 is coupled. When the electric motor 5 rotates the spindle 3, the nut 4 is moved forward or backward in the direction of the double arrow. From the thread pitch of the spindle 3 and measured by the angle measuring 7 angle change of the displacement of the needle 2 can be determined.

If the introduction of Nadei 2 into a living body, such. B. in a human back in Fig. 5 or in a forearm of FIG. 6 is to be practiced, the needle 2 is fully extended and is in the position shown in Fig. 1. The surgeon now leads the needle 2 against the body 8 and presses the needle with the medically determined force on the body surface. In order to prevent the needle piercing the outer skin in a further increase in pressure and actually penetrates into the body, a plastic disc 9 is glued to the skin at the intended injection site. This plastic disc 9 has a small recess into which the needle tip is inserted, so that slipping of the needle is avoided by the plastic disc. This plastic disc can also be replaced by a small ball attached to the tip of the needle.

The force applied by the surgeon by means of the handle on the needle force is measured by means of the force sensor 6 and fed as an electrical measurement signal to a computer. The computer has software that simulates the various material properties of the body in the form of control signals for the drive device that controls the motor 6. If z. For example, when the mode "spinal cord puncture" is set, the software activating the material properties of the body between the outer skin of the body and the spine is activated. If, on the other hand, an injection into a vein of the forearm is to be simulated, the "forearm vein injection" mode is selected.

The surgeon uses the simulation device as a real medical instrument and thus performs the same medically determined movements as under real conditions. At a predetermined pressure is simulated that the outer skin is pierced, in which the needle 2 is moved a piece into the handle. Depending on how large the puncture force was and depending on whether the surgeon continues to puncture or stop the needle, d. H. whether the piercing force is maintained or not, the needle is a larger or a small piece retracted into the handle. It is clear to the person skilled in the art of control engineering that the control loop required for this purpose must have such a dynamic behavior that the needle movements by the spindle-nut drive 3, 4, 5 must be as fast as during the movement of a real needle under real conditions.

Hereinafter, with the figures 2 to 4 further embodiments of the invention will be described. To avoid repetition, only those features and functions are described which deviate from the embodiment according to FIG.

FIG. 2 shows an embodiment of the invention in which a cable-slide arrangement 10, 11 is used as the drive device. Since, in contrast to the spindle 3 used in FIG. 1, the cable does not have sufficient inherent rigidity, a needle guide 13 in the form of a sleeve is provided for guiding the needle 2. The carriage 11 is fixed to the cable 10, which is movable by means of the motor 5 in the direction of the double arrow.

3 shows an embodiment in which the tool 2 is arranged at right angles to the handle 1, wherein the cable 10 is driven by the motor 5 and passes over two deflection rollers 12a and 12b.

Fig. 4 shows a fourth embodiment of the invention based on hydraulic cylinder-piston assemblies. The first cylinder-piston assembly is operated by means of the spindle-nut arrangement 3, 4 described in Fig. 1. The first piston 14 is connected via a piston rod 15 to the force sensor 6 and displaces hydraulic fluid in the first cylinder 16. The displaced hydraulic fluid passes via the flexible hydraulic line 17 into the second cylinder 18 and displaces there the piston 19 which is in contact with the needle 2 is connected. The principal operation of this embodiment is the same as that of the first embodiment. However, the interposed flexible hydraulic line 17 provides a decisive advantage, since now the handle 1 can be made very small, since he holds only the second cylinder-piston assembly contains.

FIGS. 5 and 6 show applications in a living human on the back and forearm.

FIG. 7 shows an embodiment of the invention using an optical navigation system 20 to 23, with which the current spatial position of the needle 2 with respect to the patient 8 is determined at a predetermined puncture site and an electrical position signal is generated, which is supplied to the arithmetic and control unit , The reference numerals 20 and 21 each indicate three navigation points, wherein the navigation points 20 define the position of the needle and the navigation points 21 the position of the patient. With the help of the cameras 22 and 23, which are in a predetermined spatial relationship to each other, the navigation points are optically detected and determines the spatial position of the needle 2. All data of the camera are fed to a computer.

The optical navigation method is well known to those skilled in the art, so that a more detailed explanation can be dispensed with. From the electrical position signal generated by the computer, it can be determined exactly whether the needle is attached to the medically correct position and at the correct angle. In this application of the invention, both a living patient or a plastic model can be used. When practicing on a live patient, the instrument tip must be provided with a stab-proof plate so that the patient is not injured by the instrument tip. FIG. 8 shows an embodiment of the invention using a torque-based navigation system. In this application of the invention, only a plastic model can be used, which has a high inherent rigidity. This plastic model is rigidly mounted on a multi-component load cell 24. When the instrument 2 is pressed by means of the handle 1 on the chest of the patient, the multi-component load cell 24 generates signals from which the touchdown point of the instrument tip is calculated. By means of a graphic animation, the correct or incorrect position of the touchdown point on the screen 25 can be displayed. Likewise, by means of an acoustic information from the speaker 26 can be informed about the correct or incorrect position of the touchdown point.

On the screen 25 it can be seen that the instrument 2 has already penetrated into the thorax.

It is clear that the controllable drive device for defined displacement of the instrument 2 with respect to the handle 1 must be technically connected to the computing and control unit. This connection can be made via an electrical control line, but also wirelessly by means of a radio link. This compound was not shown in the drawings for the sake of clarity.

It should be emphasized that with the invention, simulation devices can be provided for the first time, in which the instrument can be placed freely on any arbitrary point of a body, so that with this technology also finding the penetration point on the body and can be well practiced.

Claims

claims

A simulation device for simulating penetration of an instrument (2) into a body (8), the simulation device comprising:

- A handle (1) which is slidably connected to the instrument (2), wherein the handle (1) is held by a surgeon,

a position-determining device (7) which determines the current position of the instrument (2) with respect to the handle (1) and generates a current position signal,

a force-determining device (β) which determines the actual force with which the instrument (2) is pressed against the body (8) by means of the handle (1), the force-determining device (6) generating a current electrical force signal,

- A controllable drive device (3, 4, S, 7, 10, 11, 5, 7, W, 12, 5, 7, 3, 4, 14, 15, 16, 17, 18, 19) for the defined displacement of the instrument (2) regarding the

Handle (1) and

- A computing and control unit, the signaling technology with the drive device (3, 4, 5, 7, 10, 11, S, 7, 10, 12, 5, 7, 3, 4, 14, 15, 16, 17, 18 , 19), the computing and control unit having a memory in which body-specific puncturing information and

a computer program is stored and, starting from the current position and force signals, the drive device (3, 4, β, 7, 10, 11, 5, 7, 10, 12, β, 7, 3, 4, 14, 15 , 16, 17, 18, 19) is controlled in such a way that when the instrument (2) is pressed against the body (8), the surgeon experiences the same back pressure, ie the same haptic sensation, as in the handling of a real instrument, which in a real body is introduced.

2. Simulation device according to claim 1, characterized in that the

Drive device is arranged in or on the handle.

3. Simulation device according to claim 1 or 2, characterized in that the position detecting device is arranged in or on the handle.

4. Simulation device according to one of the preceding claims, characterized in that the force-determining device is arranged in or on the handle.

5. Simulation device according to one of the preceding claims, characterized in that a position detecting device (20, 21, 22, 23) is provided, which determines the current spatial position of the instrument tip of the instrument (2) with respect to the body (8) and an electrical position signal generated, which is the computing and control unit is supplied.

6. Simulation device according to claim 5, characterized in that navigation markings (20, 21) are provided on the handle and on the body, which are recognizable by a camera system (22, 23) for optical navigation.

7. simulation device according to claim 5, characterized in that

- A solid model body (8) is used, which is coupled to a force measuring device (24) and

in the arithmetic and control unit, a measured value processing program is imple- mented, wherein the force measuring device is designed to image and supply the forces and moments arising on contact of the model body (8) as electrical measuring signals, and the measured value processing program is designed to to determine from the measuring signals the current force application point of the instrument tip.