in fig1 , the variation in the resistance r or the change in resistance is shown against the loading due to the ground reaction force grf . in the standing phase or while standing , the normal standing phase resistance r stance is set to obtain a gait pattern that is as natural as possible with a prosthesis or orthesis during walking . if a threshold value of the ground reaction force grf is exceeded , the resistance r is raised , a continuous increasing of the resistance r up to a block resistance r block being achieved during the standing phase with increasing loading due to the ground reaction force grf . this blocking resistance r block effectively prevents a flexion of the knee joint , but is advantageously dimensioned such that no mechanical damage occurs if a loading limit for individual components of the prosthesis or orthesis is exceeded . if in the further course of events the ground reaction force grf is then reduced again , it is provided that the resistance is only reduced again from the blocking value r block when the loading has gone below the threshold value that was reached to initiate an increase in resistance . after falling below this threshold value , the resistance r is then reduced to the normal standing phase level until the standing phase resistance r stance is reached . there are various ways in which the resistance to be set can be determined ; in fig2 , form functions that can be used as factors for calculating the resistance r are represented . the curve on the right shows the function for the loading due to the ground reaction force grf , which has been normalized . the curve on the left shows how further functions f n can be entered in the calculation of the setpoint resistance . indicators for a movement of the joint , such as the knee angle velocity , the inertial angle velocity , the deviation of the distance of the ground reaction force of a joint part from the point in time of the lock coming into effect or the deviation of the inertial angle of a joint part before the lock comes into effect may serve as arguments for these functions . all of the functions f 1 to f n may be linked by multiplication to arrive at the setpoint value of the resistance , in that for example they weight the difference of a standing phase resistance from a blocking resistance and thus determine by which amount the standing phase resistance r stance is increased . the maximum value for the blocking resistance r block reduced by the value for the normal standing phase resistance r stance is multiplied by the two arguments f 1 and f n . if a function is zero , the standing phase resistance r stance remains unchanged ; as soon as all of the functions f 1 to f n are greater than 0 , the standing phase resistance r stance is increased or , if the functions become smaller , the increased resistance is reduced . the resistance r is therefore calculated from r = r stance +( r block − r stance )* f 1 ( arg 1 )* f 2 ( arg 2 )* . . . + f n ( arg n ) after reducing the resistance following activation of the block , a set of functions f n that is different from that used for activating the lock may be used . in fig3 , a schematic representation of a leg prosthesis with an upper leg shaft 1 for receiving an upper leg stump is shown . the upper leg shaft 1 is also referred to as the upper connection part . arranged on the upper connection part 1 is a lower connection part 2 in the form of a lower leg shaft with a resistance device . arranged on the lower connection part 2 is a prosthetic foot 3 . the lower connection part 2 is pivotably fastened to the upper connection part 1 by way of a joint 4 . arranged in the joint 4 is a torque sensor , which determines the effective knee torque . provided in the lower connection part 2 is a connecting part 5 to the prosthetic foot 3 , in which a device for determining the effective axial force and the ankle torque is accommodated . it is possible that not all the sensors are present in a leg prosthesis ; there may perhaps be no need for an ankle torque sensor or the knee torque sensor . apart from the resistance device , which offers the bending and stretching resistance , in the lower connection part 2 there is a control device , by way of which it is possible to change the respective resistance on the basis of the received sensor data and the evaluation of the sensor data , in that an actuator is activated in a way corresponding to the evaluation and the resistance device is set such that there is the desired or required resistance in the direction of extension and / or flexion . for this purpose , it may be provided that the sensor data are used for producing at least one auxiliary variable , which is obtained by way of a mathematical linking of two or more sensor data . this makes it possible for a number of force or torque sensors to be linked to one another to calculate forces , distances and / or torques that are not acting directly in the region of the sensors . for example , it is possible to calculate stress resultants , average torques or distances in specific reference planes , in order on this basis to be able to assess which functions must be performed at the time in question in order that a gait pattern that is as natural as possible can be achieved . referred to here as a function are those control sequences that occur in the course of a natural movement , whereas a mode is a control state that is set by an arbitrary act , for example by actuating a separate switch or by a deliberate , possibly deliberately unnatural , sequence of movements . in fig4 , it is schematically represented how the distance a of the ground reaction force vector grf from the knee axis is used as an argument . the distance a is calculated from the quotient of the knee torque m and the axial force f ax . the greater the knee torque m is in relation to the axial force f ax , the greater the distance a of the ground reaction force vector grf at the reference height , which in the present case forms the knee axis . on the basis of the argument a , it is possible to vary the stretching resistance and / or the bending resistance , since this argument a can be used to calculate whether standing applies or standing has been discontinued , so that on this basis a predetermined bending and / or stretching resistance is set . it can be determined by changing the argument a how the movement at the time in question is proceeding , so that an adaptation of the stretching and / or bending resistance can take place within the movement , including within the standing phase or the swing phase . the changing of the resistances preferably takes place continuously and in dependence on the changing of the argument or the arguments . in fig5 it is shown how the argument b in the form of the distance of the ground reaction force vector grf at a reference height from the connecting line of the torque sensors can be calculated . the argument b is calculated from b = m ⁢ ⁢ 1 + m ⁢ ⁢ 2 - m ⁢ ⁢ 1 l ⁢ ⁢ 2 - l ⁢ ⁢ 1 * ( x - l ⁢ ⁢ 1 ) fax where m 1 is the effective torque in the connecting part 5 , generally the ankle torque at the height l 1 from the floor , the torque m 2 is the knee torque at the height of the knee axis 4 , which lies at a distance of l 2 from the floor . the variable x is the reference height , the force f ax is the effective axial force within the connecting part 5 or in the lower connection part 2 . by changing the argument b , it is possible , as prescribed , to set the respective resistances and adjust them to the given changes continuously , both during the swing phase and during the standing phase . this makes it possible to activate various functions , which are automatically detected , for example a standing function that is used for example to prevent the knee joint from bending unwantedly . the increasing of the resistance , in particular the flexion resistance , during the standing phase or while standing may be implemented as a latent function that is constantly available . if the patient is in the standing phase or standing , the resistance to a flexion is automatically increased until the blocking of the joint , in particular the knee joint . the knee angle is also taken into consideration here . if , for example , the knee is in a stretched position , no locking of the flexion movement is necessary on account of the generally stable structure . if , however , the knee joint is in a slightly bent position , for example greater than 4 ° between the longitudinal extent of the lower leg part and the upper leg part , and if then there is also loading from a ground reaction force , the knee joint is then automatically locked , since it must be assumed that , in spite of the bending of the knee , no flexion is desired . in fig6 , the prosthesis is schematically represented in a sitting position . if the user of the prosthesis is in a sitting position , it is comfortable if the extension resistance and the flexion resistance of the resistance device are low , so that the movements performed during sitting , which generally have a small extent of movement , can be carried out unimpaired . to be able to carry out the changes in resistance and a determination of the state automatically , it is provided that the inertial angle α t and / or the knee angle α k are measured . the inertial angle α t of the upper leg part 1 is measured in relation to the vertical , which is assumed to be acting in the direction of gravitational force . in fig6 , this is indicated by the gravitational force vector g . assumed as the reference variable for the inertial angle α t is the longitudinal axis of the upper leg part 1 , which passes through the pivoting axis of the prosthetic knee joint 4 . in this case , the longitudinal axis corresponds approximately to the orientation of a natural upper leg bone and extends substantially centrally in relation to the upper leg part 1 , which is generally formed as an upper leg shaft . the knee angle α k lies between the longitudinal extent of the lower leg part 2 and the longitudinal extent of the upper leg part 1 . here , too , the longitudinal extent of the lower leg part 2 passes through the joint axis of the prosthetic knee joint 4 . the knee angle α k can be calculated from the inertial angle α t of the upper leg part 1 and the inertial angle α i of the lower leg part 2 , an adapted sign convention being introduced on account of the calculation of the inertial angles α t and α i on the basis of the gravitational force vector g , so that the inertial angle α t of the upper leg part 1 is obtained from the difference between the knee angle α k and the inertial angle α i of the lower leg part 2 . in addition , the ground reaction force grf or the axial force ax that is effective in the longitudinal direction of the lower leg part 2 is determined , in order to decide on the basis of the forces present whether the user of the prosthesis is in a sitting or standing position . the ground reaction force grf is generally reduced significantly when the user of the prosthesis is sitting . if , therefore , the ground reaction force grf falls below a threshold value , this is a factor in the assessment as to whether a sitting state applies . if a great ground reaction force grf is detected , a standing position can be assumed , similarly standing up can be assumed ; in both cases , it is appropriate for the flexion resistance to be increased in order to avoid unwanted collapsing or buckling under a high ground reaction force grf . an abrupt increasing of the resistance after reaching specific threshold values is often found to be uncomfortable . it is therefore provided that , after reaching a threshold value for the ground reaction force grf , the resistance is continuously increased . typically , the increasing of the resistance would be carried out between 20 % and 30 % of the bodyweight , the reduction between 20 % and 10 % of the bodyweight . if , however , there is too great a knee angle α k or inertial angle α t or if the joint 4 is moved , it can be assumed that a standing situation does not apply , so that a reduction of the resistance can be performed , possibly to an initial resistance . if the upper leg part 1 is in an inclined position , that is to say in a substantially horizontal state , so that the inertial angle α t is between for example 70 ° and 110 °, it is intended that increasing the resistance should be ruled out . it may even possibly be that , after a predetermined time has elapsed , a reduction of the resistance of the resistance device to below the standing phase resistance may be performed , since it can then be assumed that the user of the prosthesis is sitting . for determining the inertial angle velocity , the changing of the inertial angle α l over time is determined , so as to obtain an angle velocity ω 1 that can be determined in terms of the amount and direction . so if there is a specific inertial angle α 1 and a specific inertial angle velocity ω 1 , it can be assumed that there is a movement situation , that is to say not a standing situation in which locking or blocking of the knee joint would have to be performed in the case of the present method , it is provided that , immediately after loading that exceeds a specific threshold value , a lock comes into effect without any time delay , so that no separate activation of an increase in resistance has to be initiated by special movements that do not correspond to a normal sequence of movements . a loading signal that represents the magnitude of the loading is provided by way of the ground reaction force grf , the ground reaction force grf being sufficient to activate the standing function . further variables such as torques or inertial angles may be used additionally , that is to say to verify the decision as to whether a standing state or a standing phase actually applies . with the claimed method it is possible to lock the knee or some other joint in the bent position or under bending forces , the locking advantageously only coming into effect when there is a slightly bent knee , for example as from a knee bending of 4 ° as the knee angle .