WO2018004041A1

WO2018004041A1 - Medical brace manufacturing system and method

Info

Publication number: WO2018004041A1
Application number: PCT/KR2016/007105
Authority: WO
Inventors: 류홍종; 주일원; 김상준; 김동현; 서안나
Original assignee: (주)솔리드이엔지; 사회복지법인 삼성생명공익재단
Priority date: 2016-07-01
Filing date: 2016-07-01
Publication date: 2018-01-04

Abstract

Provided is a medical brace manufacturing system which includes a brace model generating system comprising: generating skeleton information of a 3D patient model of the portion of the body on which a brace is to be worn and using the information to generate at least one state coordinate system showing the posture/scale of the 3D patient model; correcting a standard model state coordinate system by using the state coordinate system of the patient model; modifying a brace model defined on the surface of the standard model, according to the correction of the standard model; applying the scale of the patient model to the modified brace model; and generating a 3D brace model by giving thickness to the brace model to which the scale of the patient model has been applied. The state coordinate system comprises multiple scale axes, and inherits the rotation amount of the joints on which they are dependent. The surface of the standard model is separated into regions in which the rotation amount of the related joint is differently inherited. The brace model comprises a design curve having multiple design points, and design point information comprises affiliated region information of the standard model surface.

Description

Medical brace production system and method

The present invention relates to a medical brace manufacturing system and method.

In manufacturing a medical aid that is used as a device for assisting or correcting a human body function, the following process is conventionally performed.

That is, a 3D image data, that is, a 3D patient model of an appearance is generated by scanning a body part of a patient to be worn by a 3D scanner using a 3D scanner, and then an operator corrects the corresponding 3D image. By creating a site design, then using a numerical control work (NC) processing equipment to manufacture the workpiece for that body site design, and then attaching and shaping the brace generating material to the exterior of the workpiece, Will produce a medical brace.

However, such a conventional medical brace manufacturing has a number of problems.

In the conventional case, there are problems in that the manufacturing time is considerably longer, as various processes, such as a process of manufacturing a workpiece for a body part and a process of forming a bone in the workpiece, are involved.

The 3D image data is simply data on the surface of the corresponding body part, and does not include skeleton structure information including joints that are closely related to the use of the brace. Accordingly, there is a limit to manufacturing a brace suitable for a patient.

In addition, the creation of the body part design can not only depend entirely on the experience of the operator, there is a problem that the deviation occurs in the brace according to the operator, it is difficult to secure product reliability. Moreover, as the process of shaping the bone is performed manually for the manufacture of the brace, a problem arises in that it is difficult to secure the reliability of the product.

As such, when the reliability of the product is not secured, when the brace is not suitable after being worn on the patient, a troublesome manufacturing process needs to be performed again.

As described above, according to the conventional manufacturing method of the auxiliary device, a problem occurs such that manufacturing efficiency is lowered and product reliability is not secured.

The present invention has a problem to provide a way to improve the manufacturing efficiency of the brace and ensure the reliability.

In order to achieve the task as described above, the present invention generates skeleton information of the 3D patient model for the body part to be worn by the brace and use it to generate at least one state coordinate system representing the posture / scale of the 3D patient model. and; Correct the state coordinate system of the standard model with the state coordinate system of the patient model; Modifying the brace model defined on the standard model surface according to the calibration of the standard model; Apply the scale of the patient model to the modified brace model; And a brace model generation system for generating a 3D brace model by applying thickness to the brace model to which the patient model scale is applied, wherein the state coordinate system includes a plurality of scale axes and inherits the amount of rotation of the joint to which the brace model depends. The surface of the model is divided into regions in which the amount of rotation of the associated joint is inherited differently, and the brace model includes a design curve having a plurality of design points, and the design point information includes the region information of the standard model surface to which it belongs. It provides a medical brace manufacturing system having.

The brace model generation system corrects the posture of the patient model, and according to the correction can correct the brace model to which the scale of the patient model is applied.

The design point information may include projection direction information onto the patient model surface.

The brace model may include a design option that includes at least one of thickness control, vents, holes, initials, and accessories.

The brace model generation system generates a plurality of reference point information using a plurality of marks displayed on the surface of the 3D patient model and generates the skeleton information based on the reference point information, wherein the plurality of reference point information is the body part. It may include joint reference point information located therein.

The body part is a lower limb of the knee or less, and the at least one state coordinate system includes: a first state coordinate system dependent on the femoral joint, a second state coordinate system dependent on the subtalar joint, and a third state coordinate system dependent on the toe joint. It may include.

The plurality of scale axes of the first state coordinate system are the + X1 axis, the -X1 axis, the + Y1 axis, the -Y1 axis, and the + Z1 axis having the reflux joint reference point as the origin, and the scale of the + Z1 axis is the knee joint reference point from the corresponding origin. Corresponds to the distance to, the scale of the + Y1 axis corresponds to the distance from the origin to the outer end of the retreat joint, the scale of the -Y1 axis corresponds to the distance from the origin to the medial end of the femur The scale of the + X1 axis corresponds to the distance from the origin to the patient model surface point that is encountered in the projection in the + X1 axis direction, and the scale of the -X1 axis is the patient model that meets in the projection in the -X1 axis direction from the origin. It may correspond to the distance to the surface point.

The plurality of scale axes of the second state coordinate system are + X2 axis, + Y2 axis, -Y2 axis, and + Z2 axis whose origin is outside the heel vicinity, and the scale of the + Z2 axis is from the origin to the subtalar joint reference point. A distance of the + Y2 axis corresponds to a distance from a corresponding origin to a toe joint outer end, a scale of the -Y2 axis corresponds to a distance from a corresponding origin to a toe joint inner end, and a scale of the + X2 axis May correspond to the distance from the origin to the toe joint reference point.

The plurality of scale axes of the third state coordinate system are + X3 axis, + Y3 axis, -Y3 axis, + Z3 axis, and -Z3 axis having the toe joint reference point as the origin, and the scale of the + X3 axis is from the origin to the toe end point. Corresponds to a distance of, and the scale of the + Y3 axis corresponds to the distance from the origin to the outer end of the toe joint, and the scale of the -Y3 axis corresponds to the distance from the origin to the inner end of the toe joint, The scale corresponds to the distance from the origin to the patient model surface point that is encountered in the projection in the + Z3 axis direction, and the scale of the -Z3 axis is from the origin to the patient model surface point that is met in the projection in the -Z3 axis direction. It may correspond to the distance of.

A 3D scanner scanning the body part to generate a 3D image; It may include a 3D printer receiving the 3D brace model information to manufacture the brace.

In another aspect, the present invention, in the orthotic model generation system, generates skeleton information of the 3D patient model for the body part to be worn by the brace and use it to generate at least one state coordinate system representing the posture / scale of the 3D patient model Making a step; Correcting the state coordinate system of the standard model with the state coordinate system of the patient model; Modifying the brace model defined on the standard model surface according to the calibration of the standard model; Applying the scale of the patient model to the modified brace model; Generating a 3D brace model by applying thickness to the brace model to which the patient model scale has been applied, wherein the state coordinate system includes a plurality of scale axes and inherits the amount of rotation of the joint to which the patient model scale is dependent, and the surface of the standard model. Is divided into regions in which the amount of rotation of an associated joint is inherited differently, and the orthotic model includes a design curve having a plurality of design points, wherein the design point information includes medical information having area information of the standard model surface to which it belongs. Provide a production method.

In the orthotic model generation system, the posture of the patient model may be corrected, and the orthotic model to which the scale of the patient model is applied may be corrected according to the calibration.

Generating a 3D image by scanning the body part using a 3D scanner; The 3D printer may include receiving the 3D brace model information and manufacturing the corresponding brace.

In another aspect, the present invention provides a computer readable recording medium having recorded thereon a program for performing the above-described method for manufacturing a medical brace.

According to the present invention, the skeleton information of the 3D patient model for the body part to be worn is generated and used to generate at least one state coordinate system representing the posture / scale of the 3D patient model, and the state coordinate system of the standard model is used. 3D by calibrating the model with the state coordinate system, transforming the brace model defined on the standard model surface according to the calibration of the standard model, scaling the brace model to the brace model, and giving thickness to the brace model with the patient model scale applied. A brace model may be generated, and the brace may be manufactured using the generated 3D brace model.

Accordingly, it is possible to manufacture the brace optimized for the brace wearer, it is possible to maximize the reliability of the brace manufacturing.

In addition, the orthotic modeling application allows you to create orthotic models in a very short time and then use the orthotic manufacturing equipment to immediately build the orthosis, which significantly shortens and streamlines the orthotic manufacturing process. Can be.

1 is a view schematically showing a medical brace manufacturing system according to an embodiment of the present invention.

2 is a flow chart schematically showing a method for manufacturing a medical brace according to an embodiment of the present invention.

Figure 3 is a schematic diagram of the skeleton information and state coordinate system of the lower limb standard model according to an embodiment of the present invention.

FIG. 4 is a schematic view of surface regions divided by the amount of change in joint rotation for a lower limb standard model according to an embodiment of the invention. FIG.

5 is a view schematically showing the design curve and the projection direction of the brace model according to an embodiment of the present invention.

6 is a view schematically showing the thickness control of the brace model according to an embodiment of the present invention.

7 is a view schematically showing the vent of the brace model according to an embodiment of the present invention.

8 is a view schematically showing a hole in the brace model according to an embodiment of the present invention.

9 schematically illustrates the initials of a brace model according to an embodiment of the invention.

10 is a schematic illustration of the accessories of the brace model according to an embodiment of the invention.

Hereinafter, embodiments of the present invention will be described in detail with reference to the drawings.

The medical orthosis manufactured according to the present invention may correspond to an orthosis applied to not only a human but also an animal, and also may correspond to all kinds of orthosis worn on all body organs to which the orthosis can be applied. For convenience of explanation, a description will be given taking an brace worn on a person's lower leg as an example.

1 is a view schematically showing a medical brace manufacturing system according to an embodiment of the present invention, Figure 2 is a flow chart schematically showing a method for manufacturing a medical brace according to an embodiment of the present invention.

Referring to FIG. 1, the medical assistive device manufacturing system 10 according to an exemplary embodiment of the present invention 3D scans a body part to be worn by the assistive device to generate and output 3D image data of an appearance of the corresponding area 3D scanner 100. ), The brace model generation system 200 for generating a 3D brace model using the 3D image data output from the 3D scanner 100 and the brace manufacturing equipment 300 for receiving the 3D brace model and manufacturing the brace. It may include.

In this case, the brace model generation system 200 may be a computing processor such as a computer as a means for generating a brace model by loading the brace model generation application and performing a calculation process according to the application. Such an arithmetic processing apparatus may include a main body which performs arithmetic processing, a monitor which is an image output apparatus displaying an image, and an input apparatus such as a keyboard or a mouse which processes an input operation of an operator.

In addition, a 3D printer may be used as the auxiliary manufacturing equipment 300.

Hereinafter, the assistive device manufacturing system 10 and the assistive device manufacturing method using the same will be described in more detail.

Regarding the manufacture of the brace, a process of setting a brace model corresponding thereto based on a standard model of a body part to be worn by the brace may be performed (S10). Here, the brace model may include, for example, design curve information and option information as additional information as the appearance design information, and design curves and options may be selected in the process of setting the brace model.

Meanwhile, the standard model and the brace model template thereof may be generated in advance and stored in a storage means in the brace model generation system 200 or an external storage means.

Here, the standard model is a model representing the lower extremity of a normal person may include appearance information and skeleton information. In relation to the generation of the standard model, for example, 3D scanning of the lower extremity of a normal person selected as a sample is performed by 3D scanning through the 3D scanner 100 to generate a 3D image of the standard model, and the brace model generation system 200 ) Can be printed.

In this case, the 3D image has only appearance information. In order to identify the internal skeleton structure and generate related information from the 3D image, a plurality of marks may be displayed on the 3D image for specifying joints located in the lower limb. have.

In this regard, for example, the marks may include a mark that is directly marked by using a marking pen or the like on the lower skin by a medical staff such as a doctor before scanning through the 3D scanner 100, that is, the first mark. In addition, a mark marked by using an input device such as a mouse or the like may be included on the skin surface of the generated 3D image. Of course, in some cases, the first mark

As such, skeleton information of the lower limb may be generated through the marks displayed on the 3D image of the standard model. In this regard, the skin surface of the 3D image is marked with a number of marks for specifying this in relation to a number of joints located in the lower limbs, and the mark information is used to generate reference points for generating a suitable brace model. By connecting these reference points, a skeleton line of the lower limb can be created.

Here, a number of joints of the lower extremities include a knee joint, a talocrural joint associated with vertical rotation as a joint associated with the rotation of the ankle, a subtalar joint associated with left and right rotation, and an entire toe. And toe joints associated with vertical rotation.

In addition, the plurality of reference points may include joint center points, which are joint reference points CK, CT, CS, and CP for specifying each joint or each joint axis, and further, the lower coordinate coordinate system BA for expressing the lower limbs in a coordinate system. It may include a reference point (CE) indicating the origin (O) and the toe tip.

These reference points may be generated using the marks P1 to P5, P7, and P8 displayed on the 3D image.

In this regard, referring to the left figure of FIG. 3, for example, in relation to generating a reference point CK for the knee joint, the knee joint axis AK which is a line connecting the inner and outer end marks P1 and P2 of the knee joint. ) Is defined as the reference point (CK) for the joint.

In relation to generating the reference point CT for the rejection joint, the center point of the rejection joint axis AT, which is a line connecting the inner and outer end marks P3 and P4 of the rejection joint, is the reference point CT for the joint. Is defined as

Next, in connection with creating a reference point (CS) for the subtalar joint, a line is formed between the instep end mark (P5) of the subtalar joint and the end point mark (not shown) of the heel and the specific point on the XY plane of the origin coordinate system. As an angle, for example, about 23 degrees is rotated clockwise (ie, from the heel to the outside) with respect to the instep end mark P5 of the subtalar joint, which is defined as the subtalar joint axis AS. . At this time, the point (P6) where the subtalar joint axis (AS) meets the rear surface of the heel is also defined, the distance to the inferior end mark (P5) of the subtalar joint: the subtalar joint axis (AS) and the rear surface of the heel The point where the distance to the meeting point P6 is 3: 7 is defined as the reference point CS for the joint AS.

Next, in relation to generating a reference point (CP) for the toe joint, the toe joint medial end mark (ie, the big toe main joint medial end mark) (P7) and the toe joint lateral tip mark (ie, the young toe main joint) The center point of the toe joint axis AP, which is the line connecting the outer end mark) P8, is defined as the reference point CP for the joint.

On the other hand, in relation to generating the lower coordinate system origin (O), a line perpendicular to the sole plane, that is, the XY plane and passing through the heel trailing mark (not shown) is defined as the Z axis of the coordinate system origin (O), which is the Z axis. The point of the plantar plane that meets can be defined as the origin (O). That is, the coordinate system origin O of the standard model may be defined outside the model near the heel back.

Meanwhile, in the drawing, P9 may be displayed on the image by the operator as the toe end point or automatically detected by image processing, and the toe reference point CE may be defined by this toe end point P9.

As described above, the skeleton structure can be identified and specified. In this regard, it creates a connecting line connecting the knee joint reference point (CK) and the decline joint reference point (CT) and defines it as the tibial bone line (BK), and connects the decline joint reference point (CT) and the subtalar joint reference point (CS). Create a connection line and define it as an ankle line (BT), create a connection line between the subtalar joint reference point (CS) and the toe joint reference point (CP), and define it as the femur line (BS), and define the toe joint reference point ( CP) and toe reference point (CE) to create a connecting line can be defined as a toe bone line (BP).

In particular, in the present embodiment, after generating the skeleton information as described above, based on this as a plurality of state coordinate system indicating the state of the standard model, that is, the posture (or joint rotation amount) and scale, for example, as shown in FIG. The first to third state coordinate systems AXIS_T, AXIS_B and AXIS_P may be generated as shown in the drawing on the right.

The first state coordinate system AXIS_T is configured to have the five joint axes (that is, the scale axes) as the origin of the joint joint reference point CT, and may be dependent on the joint joint. The first state coordinate system AXIS_T reflects the rotation of the rejection joint axis AT so that the corresponding coordinate system can rotate, and the rotation amount of the rejection joint axis AT is inherited by the first state coordinate system AXIS_T. . Therefore, when the decline joint axis AT rotates, all five coordinate axes constituting the first state coordinate system AXIS_T rotate with the decline joint axis AT as the rotation axis.

As five coordinate axes of the first state coordinate system AXIS_T, the + X1 axis, the -X1 axis, the + Y1 axis, the -Y1 axis, and the + Z1 axis can be used. In this case, the scale or size of the + Z1 axis may correspond to a distance from the reflux joint reference point CT, which is the corresponding origin, to the knee joint reference point CK. The scale of the + Y1 axis corresponds to the distance from the rejection joint reference point CT to the outer end mark P4 of the rejection joint, and the scale of the -Y1 axis is from the rejection joint reference point CT to the medial end mark P3 of the rejection joint. It may correspond to the distance of, and the directions of the + Y1 axis and -Y1 axis may be opposite to each other. The scale of the + X1 axis may correspond to the distance from the corresponding origin (CT) to the standard model skin surface point encountered when projecting in the + X1 axis direction, and the scale of the -X1 axis is projected from the origin CT in the -X1 axis direction. It may correspond to the distance to the standard model skin surface point that meets the time.

Next, the second state coordinate system AXIS_B is located outside the heel so that, for example, the coordinate system origin O of the standard model is the origin of the second state coordinate system AXIS_B and has four coordinate axes (that is, scale axes). And subordinate to subtalar joints. The second state coordinate system AXIS_B reflects the rotation of the subtalar joint axis AS so that the corresponding coordinate system can rotate, and the amount of rotation of the subtalar joint axis AS is transmitted to the second state coordinate system AXIS_B. Inherited. Therefore, when the subtalar joint axis AS rotates, all four coordinate axes constituting the second state coordinate system AXIS_B rotate with the subtalar joint axis AS as the rotation axis.

Furthermore, since the subtalar joint is subordinate to the relatively upper layer of the degenerate joint and reflects the movement of the degenerative joint, the lower layer of the subtalar joint axis (AS) is the upper layer. Will inherit the amount of rotation. As such, the second state coordinate system AXIS_B, which depends on the subtalar joint axis AS, inherits the rotation amount of the femoral joint axis AT.

As four coordinate axes of the second state coordinate system AXIS_B, the + X2 axis, the + Y2 axis, the -Y2 axis, and the + Z2 axis can be used. In this case, the scale or size of the + Z2 axis may correspond to a distance from the corresponding origin O to the subtalar joint reference point CT. The scale of the + Y2 axis corresponds to the distance from the origin (O) to the toe joint outer end mark (P8), and the scale of the -Y2 axis corresponds to the distance from the origin (O) to the toe joint inner end mark (P7). The directions of the + Y2 axis and the -Y2 axis may be opposite to each other. The scale of the + X2 axis may correspond to the distance from the corresponding origin O of the + X2 axis to the toe joint reference point CP.

Next, the third state coordinate system AXIS_P is configured to have the toe joint reference point CP as the origin of the coordinate system and have five coordinate axes (that is, scale axes), and may be dependent on the toe joint. The third state coordinate system AXIS_P reflects the rotation of the toe joint axis AP so that the corresponding coordinate system can rotate, and the amount of rotation of the toe joint axis AP is inherited by the third state coordinate system AXIS_P. . Therefore, when the toe joint axis AP rotates, all five coordinate axes constituting the third state coordinate system AXIS_P rotate with the toe joint axis AP as the rotation axis.

Furthermore, the toe joints are subordinate to the upper and lower tibial joints because of the characteristics of the body structure. The rotation amount of AT and the rotation amount of the subtalar joint axis AS are inherited. As such, the third state coordinate system AXIS_P, which is dependent on the toe joint axis AP, inherits the amount of rotation of the hip joint axis AT and the amount of rotation of the subtalus joint axis AS.

As five coordinate axes of the third state coordinate system AXIS_B, the + X3 axis, the + Y3 axis, the -Y3 axis, the + Z3 axis, and the -Z3 axis can be used. In this case, the scale or size of the + X3 axis may correspond to a distance from the corresponding origin CP to the toe end point CE. The scale of the + Y3 axis corresponds to the distance from the origin (CP) to the toe joint outer end mark (P8), and the scale of the -Y3 axis corresponds to the distance from the origin (CP) to the toe joint inner end mark (P7). The directions of the + Y3 axis and the -Y3 axis may be opposite to each other. The scale of the + Z3 axis can be the distance from the corresponding origin point (CP) of the + Z3 axis to the standard model skin surface point encountered when projecting in the + Z3 axis direction, and the scale of the -Z3 axis is -Z3 axis direction from the corresponding origin point (CP). Can be the distance to the standard model skin surface point encountered during projection.

Through the first to third state coordinate systems AXIS_T, AXIS_B, and AXIS_P generated as described above, the state of the standard model, that is, the attitude and scale, can be defined.

The first to third state coordinate systems AXIS_T, AXIS_B, and AXIS_P may be used as comparison means for comparing postures between the standard model and the patient model described later.

On the other hand, the standard model may include information on the surface deformation according to the posture change, that is, the joint rotation, as the region-specific information of the skin surface. In this regard, referring to FIG. 4, the skin surface of the standard model, in consideration of the rotation of the corresponding joint axes, is a so-called rotational non-deformation area in which the skin surface is areas that are not substantially deformed (ie, contracted or relaxed) with rotation. And the skin surface may be divided into so-called rotational deformation regions, which are regions deformed by rotation. That is, the rotational deformation area and the rotational deformation area are defined by reflecting the characteristics of the body structure.

In this regard, the rotational non-deformation areas are areas above the ankle joint (ie, the hip joint and the subtalar joint) that reflect substantially 100% of the ankle rotation, that is, inherit the first rotational non-deformation area (not deformed by rotation). Ar_AT), a second rotational non-deformation area (Ar_AS) that substantially inherits 100% of the ankle left and right as an area under the ankle joint, and a third rotational non-deformation area that inherits 100% of the toe up and down rotation as an area below the toe joint. (Ar_AP). Meanwhile, the first rotational non-strain area Ar_AT inherits the scale and position of the first state coordinate system AXIS_T, and the second rotational non-strain area Ar_AS inherits the scale and position of the second state coordinate system AXIS_B. The third rotational non-deformation area Ar_AP inherits the scale and position of the third state coordinate system AXIS_P.

In addition, the rotational deformation regions correspond to the ankle joint region, and the first rotational deformation region Ar_TS, which is an area that simultaneously receives the vertical rotation and the left and right rotation of the ankle at a predetermined ratio, and the toe vertical rotation as the region corresponding to the toe joint region. And the second rotation deformation region Ar_SP, which is a region that is deformed by simultaneously receiving left and right rotations of the ankle at a predetermined ratio. In this case, the first rotational deformation area Ar_TS is defined between the first rotational deformation area Ar_AT and the second rotational deformation area Ar_AS, and the second rotational deformation area Ar_SP is the second rotational deformation area Ar_AS. And a third rotational non-strain area Ar_AP. The first and second rotation deformation regions Ar_TS and Ar_SP may not reflect 100% of the rotation amount of the corresponding joints, but may reflect a predetermined ratio lower than this, and the ratio may be differentiated according to the position. Meanwhile, the first rotational deformation region Ar_TS inherits the scale and position of the second state coordinate system AXIS_B, and the second rotational deformation region Ar_SP inherits the scale and position of the third state coordinate system AXIS_P. do.

As such, the skin surface of the lower limb has a characteristic that the rotation amount of the joints related to each position is more specifically inherited and reflected in each region. It can be divided into deformation areas.

Thus, if the brace model is generated based on the standard model reflecting the deformation characteristics of the skin surface due to the rotation of the joint, even if the standard model is transformed into the patient posture, the surface deformation amount according to the deformed posture can be reflected in the brace model. Will have As such, the standard model includes information on the amount of surface deformation according to the change of attitude.

An orthotic model template for the standard model may be generated based on the standard model information as described above. The orthotic model template may register a design curve that is an external design component of the orthotic model and a design option that is an additional design component. Here, the design options may include, for example, option items such as adjusting the thickness of the brace model and vents, holes, patient initials, and accessories disposed inside the brace model.

As such, the design components of the brace model template are defined on the surface of the standard model, so that the surface change of the standard model according to the posture / scale deformation of the standard model is reflected in the design components. That is, the template design elements inherit the surface area of the standard model to which they belong, that is, the information of the belonging area, and the surface change of the belonging area is reflected.

As described above, with respect to the brace model template generated as described above, the operator can select and set a design curve registered in the template and select and set a design option to set the brace model for the standard model.

After setting the brace model as described above, the patient model, which is a lower limb model of the patient, is generated in a similar manner to the generation of the standard model (S20). That is, a 3D image is generated by scanning a patient through a 3D scanner, and skeleton information of the patient model is generated using the 3D scanner to generate first to third state coordinate systems AXIS_T, AXIS_B, and AXIS_P.

Next, the process of comparing the rotation of the posture, that is, the joint between the patient model and the standard model is performed (S30). That is, the first to third state coordinate systems AXIS_T, AXIS_B, and AXIS_P may be compared between the patient model and the standard model, and thus the amount of rotation of each coordinate system may be calculated.

As such, when the amount of rotation is calculated, the process of aligning the posture of the standard model with the posture of the patient model is performed (S40). That is, the first to third state coordinate systems AXIS_T, AXIS_S and AXIS_P of the standard model are corrected by the amount of rotation.

Next, the brace model for the standard model is corrected according to the standard model whose posture is corrected (S50). That is, the skin surface deformation of the posture corrected standard model is applied to the design curve and design options of the brace model, so that the posture of the brace model is modified to fit the corrected standard model.

Next, a process of mapping the corrected brace model according to the posture of the patient model to the patient model is performed (S60). In this mapping process, the scale of the patient model is reflected in the brace model. The scale of the brace model is changed to the scale of the patient model to apply the brace model on the surface of the patient model.

The scale application in this process may be performed by reflecting the scale difference of the state coordinate systems AXIS_T, AXIS_B and AXIS_P between the standard model and the patient model.

In this case, the projection direction of the brace model for changing the scale of the brace model in the thickness direction plane, that is, the cross-sectional reference of the lower surface, may be defined by the operator, and with reference to FIG. 5.

5 shows the design curve DCv of the brace model defined on the standard model surface, and the design curve DCv on the cross section cut along the cutting line CC in the thickness direction of the lower limb in the right figure. The projection on the model surface is shown.

Here, the design curve DCv may be composed of lines connecting a plurality of design points DP and neighboring design points DP defining its shape. Each design point DP includes the belonging region information, the position of which is deformed according to the deformation of the skin surface of the belonging region, and thus the corresponding design curve DCv can be deformed.

Furthermore, the design point DP includes projection direction information for changing the thickness direction scale, where the projection direction is set by the operator in a direction perpendicular to the standard model skin surface (ie normal direction) or at an angle different from that. Can be.

As such, when the projection direction can be adjusted by the operator, it is possible to implement this when it is necessary to maintain a constant shape or distance with respect to a specific part of the brace model. For example, as shown in Fig. 5, for two design points DP of the standard model, the projection direction is defined so that they are projected in the same B2 direction without defining the projection direction in the B1 direction perpendicular to the corresponding skin surface. In this case, the two design points DP can maintain the same distance on the skin surface.

Next, a process of correcting the posture of the patient model may be performed, and accordingly, the brace model whose scale is changed may also be changed to the corrected posture (S70). In this regard, the patient's posture is likely to be different from what is desired according to the physical defect of the patient or the surrounding environment during 3D scanning, and the posture change may be required according to the degree of body part correction. Accordingly, by adjusting the angle of the joint with respect to the patient model can be performed to correct the posture, this posture correction information is reflected in the brace model, the brace model can be changed.

Next, a cutting operation is performed to remove the remaining areas other than the area occupied by the brace model from the patient model on which the brace model is worn, thereby leaving the brace model area, which is the area occupied by the brace model (S80). Thereafter, the 3D brace model can be finally generated by giving a thickness to the brace model region to make it 3D (S90).

That is, the surface area for the brace model is shown by the cutting operation, and the 3D brace model can be generated by giving thickness to the brace model.

On the other hand, with respect to the thickness of the brace model, as described above, when the thickness adjustment item of the design option item is selected, it is possible to adjust the thickness for a portion of the brace model.

In this regard, with reference to FIG. 6, for example, the brace model has a default thickness d1 set by default. The operator may set to select a specific area A3 for thickness adjustment. Accordingly, the area A3 may be set to have a thickness d2 smaller than the base thickness d1, and the thickness d2 of the area A3 may be set by an operator. On the other hand, when the selection area A3 and the basic area A1 of the default thickness d1 are directly brought into contact with each other, the thickness changes rapidly between these areas, which may cause a brace defect or wearer discomfort. Therefore, between the selection area A3 and the basic area A1, a buffer area A2 is set to have a constant width so that the thickness can be continuously changed smoothly. In this buffer area A2, the thickness changes in a curved form. can do.

Meanwhile, other design option items other than the thickness adjustment item will be described below.

With reference to the vent item, reference may be made to FIG. 7, wherein FIG. 7 (a) is a side view and FIG. 7 (b) is a sectional view. The operator can select the vent item and set an area R1 for the creation of the vent K1 on the standard model surface. In this regard, for example, in setting the vent opening area R1, an operator may designate a plurality of area points RP and thus an area curve connecting the area points RP may be generated. The vent opening area R1 defined by the above may be set.

In the vent opening region R1, the vent opening K1 may be disposed at a predetermined distance (i) from the skin surface, and a reference point PP1 may be displayed at the center of each vent opening K1. have. Here, the reference point PP may be used as a reference point for the interval i between the vents K1. On the other hand, when the ventilation opening K1 spans the area curve that is the boundary of the ventilation opening generating region R1, the ventilation opening may be configured not to be included (see the ventilation opening shown by the dotted line in Fig. 7A).

Such an air vent item may include, for example, air vent generation area curve information, air vent shape information, size information such as air vent diameter t, air vent spacing information, and belonging region information which is a standard model surface area to which the air vent belongs. .

Next, reference may be made to FIG. 8 with respect to a hole item, in which FIG. 8 (a) is a side view and FIG. 8 (b) is a cross-sectional view. The operator can select a hole item and set the hole K2 to the standard model surface. Accordingly, the hole K2 may be generated at the set position, and a reference point PP2 thereof may be displayed at the center of the hole K2. Here, the reference point PP2 may be used as a picking reference point for forming the hole K2 in the brace model.

In this case, the projection direction of the hole K2 on the skin surface and the picking direction for forming the hole K2 may be normal directions based on the hole reference point PP2, but the present invention is not limited thereto.

The hole K2 may be rotated by rotating the hole reference point PP2.

Such a hole item may include, for example, hole reference point position / rotation information, hole shape information, size information such as hole diameter, hole projection direction information, and belonging region information which is a standard model region to which the hole belongs.

Next, reference may be made to FIG. 9 with respect to the initial item, in which FIG. 9 (a) is a side view and FIG. 9 (b) is a sectional view. The operator can select the initial item and set the patient's initials K3 to the standard model surface. Accordingly, the initial K3 may be generated at the set position, and the reference point PP3 thereof may be displayed at the center of the initial K3.

Here, in applying the initial K3 to the auxiliary model, the projection direction of the initial K3 (that is, the projection direction of each word CH of the initial K3) is the normal direction based on the initial reference point PP3. It may be, but is not limited thereto.

The initial reference point PP3 may be rotated to rotate the initial K3.

Such initial items may include, for example, initial word information, initial position / rotation information, initial size information, initial projection direction information, and belonging area information which is a standard model area to which the initial belongs.

Next, reference may be made to FIG. 10 regarding the accessory item. The operator can select the accessory item and set the accessory (K4) to the standard model surface. Accordingly, the accessory K4 may be generated at the set position, and the reference point PP4 thereof may be displayed at the center of the accessory K4.

Here, in applying the accessory K4 to the brace model, the projection direction of the accessory K4 may be a normal direction based on the accessory reference point PP4, but is not limited thereto.

In addition, the accessory K4 may be rotated by rotating the accessory reference point PP4.

Such an accessory item may include, for example, accessory position / rotation information, accessory size information, accessory projection direction information, and belonging area information that is a standard model region to which the accessory belongs.

As described above, according to an embodiment of the present invention, the skeleton information of the 3D patient model for the body part to be worn is generated and used to generate at least one state coordinate system representing the posture / scale of the 3D patient model. The state coordinate system of the standard model is calibrated with the state coordinate system of the patient model, the brace model defined on the standard model surface is modified according to the calibration of the standard model, the scale of the patient model is applied to the brace model, and the patient model scale is applied. The 3D brace model can be generated by adding thickness to the brace model, and the brace may be manufactured using the generated 3D brace model.

On the other hand, the medical orthosis manufacturing system and method according to the above-described embodiment, can be similarly applied to the production of orthosis for various areas, such as the human limbs, neck. In addition, it can be applied to the production of orthosis for animals as well as humans.

Meanwhile, the method for manufacturing a medical brace according to the embodiment of the present invention may be implemented in the form of program instructions that can be executed by various computer means and recorded in a computer readable medium. Computer-readable media may include, alone or in combination with the program instructions, data files, data structures, and the like. The program instructions recorded on the media may be those specially designed and constructed for the present invention, or they may be of the kind well-known and available to those having skill in the computer software arts. Examples of computer-readable recording media include magnetic media such as hard disks, floppy disks, and magnetic tape, optical media such as CD-ROMs, DVDs, and magnetic disks, such as floppy disks. Magneto-optical, and ROM, RAM, flash memory and the like. Examples of program instructions include not only machine code generated by a compiler, but also high-level language code that can be executed by a computer using an interpreter or the like. The hardware device described above may be configured to operate as one or more software modules to perform the operations of one embodiment of the present invention, and vice versa.

Claims

Generate skeleton information of the 3D patient model for the body part to be worn with the brace and use the same to generate at least one state coordinate system representing the pose / scale of the 3D patient model; Correct the state coordinate system of the standard model with the state coordinate system of the patient model; Modifying the brace model defined on the standard model surface according to the calibration of the standard model; Apply the scale of the patient model to the modified brace model; And a brace model generation system for generating a 3D brace model by applying a thickness to the brace model to which the patient model scale is applied.

The state coordinate system includes a plurality of scale axes and inherits the rotation amount of the joints to which the state coordinates depend;

The surface of the standard model is divided into regions in which the amount of rotation of the associated joint is inherited differently,

The brace model includes a design curve having a plurality of design points, the design point information having area information of the surface of the standard model to which it belongs.

Medical brace production system.
The method of claim 1,

The brace model generation system corrects the posture of the patient model, and according to the correction to correct the brace model to which the scale of the patient model is applied

Medical brace production system.
The method of claim 1,

The design point information includes projection direction information onto the patient model surface.

Medical brace production system.
The method of claim 1,

The brace model includes a design option that includes at least one of thickness control and vents, holes, initials, and accessories.

Medical brace production system.
The method of claim 1,

The brace model generation system,

Generate a plurality of reference point information using a plurality of marks displayed on the surface of the 3D patient model and generate the skeleton information based on this reference point information,

The plurality of reference point information includes joint reference point information located inside the body part.

Medical brace production system.
The method of claim 1,

The body part is the lower extremity below the knee,

The at least one state coordinate system includes a first state coordinate system subordinate to the femoral joint, a second state coordinate system subordinate to the subtalus joint, and a third state coordinate system subordinate to the toe joint

Medical brace production system.
The method of claim 6,

The plurality of scale axes of the first state coordinate system are + X1 axis, -X1 axis, + Y1 axis, -Y1 axis, and + Z1 axis having the reflux joint reference point as the origin,

The scale of the + Z1 axis corresponds to the distance from the corresponding origin to the knee joint reference point,

The scale of the + Y1 axis corresponds to the distance from the origin to the outer end of the hip joint,

The scale of the -Y1 axis corresponds to the distance from the origin to the inner end of the femoral fracture,

The scale of the + X1 axis corresponds to the distance from the origin to the point of the patient model surface that meets when projecting in the + X1 axis direction,

The scale of the -X1 axis corresponds to the distance from the corresponding origin to the point of the patient model surface that meets during projection in the -X1 axis direction.

Medical brace production system.
The method of claim 6,

The plurality of scale axes of the second state coordinate system are + X2 axis, + Y2 axis, -Y2 axis, and + Z2 axis having the origin outside the heel vicinity,

The scale of the + Z2 axis corresponds to the distance from the origin to the subtalar joint reference point,

The scale of the + Y2 axis corresponds to the distance from the origin to the outer end of the toe joint,

The scale of the -Y2 axis corresponds to the distance from the origin to the inner end of the toe joint,

The scale of the + X2 axis corresponds to the distance from the origin to the toe joint reference point

Medical brace production system.
The method of claim 6,

The plurality of scale axes of the third state coordinate system are + X3 axis, + Y3 axis, -Y3 axis, + Z3 axis, and -Z3 axis having the toe joint reference point as the origin,

The scale of the + X3 axis corresponds to the distance from the origin to the toe end point,

The scale of the + Y3 axis corresponds to the distance from the origin to the outer end of the toe joint,

The scale of the -Y3 axis corresponds to the distance from the origin to the inner end of the toe joint,

The scale of the + Z3 axis corresponds to the distance from the corresponding origin to the point of the patient model surface that meets when projecting in the + Z3 axis direction,

The scale of the -Z3 axis corresponds to the distance from the corresponding origin to the point of the patient model surface that meets during projection in the -Z3 axis direction.

Medical brace production system.
The method of claim 1,

A 3D scanner scanning the body part to generate a 3D image;

3D printer for manufacturing the brace by receiving the 3D brace model information

Medical aids production system comprising a.
In the brace model generation system,

Generating skeleton information of the 3D patient model for the body part to be worn by the brace and using the same to generate at least one state coordinate system representing the posture / scale of the 3D patient model; Correcting the state coordinate system of the standard model with the state coordinate system of the patient model; Modifying the brace model defined on the standard model surface according to the calibration of the standard model; Applying the scale of the patient model to the modified brace model; Generating a 3D brace model by applying a thickness to the brace model to which the patient model scale is applied;

The state coordinate system includes a plurality of scale axes and inherits the rotation amount of the joints to which the state coordinates depend;

The surface of the standard model is divided into regions in which the amount of rotation of the associated joint is inherited differently,

The brace model includes a design curve having a plurality of design points, the design point information having area information of the surface of the standard model to which it belongs.

How to make a medical brace.
The method of claim 11,

In the brace model generation system, correcting the pose of the patient model,

Calibrating the brace model to which the scale of the patient model is applied according to the calibration.

How to make a medical brace.
The method of claim 11,

The design point information includes projection direction information onto the patient model surface.

How to make a medical brace.
The method of claim 11,

The brace model includes a design option that includes at least one of thickness control and vents, holes, initials, and accessories.

How to make a medical brace.
The method of claim 11,

The brace model generation system generates a plurality of reference point information using a plurality of marks displayed on the surface of the 3D patient model and generates the skeleton information based on the reference point information,

The plurality of reference point information includes joint reference point information located inside the body part.

How to make a medical brace.
The method of claim 11,

The body part is the lower extremity below the knee,

The at least one state coordinate system includes a first state coordinate system subordinate to the femoral joint, a second state coordinate system subordinate to the subtalus joint, and a third state coordinate system subordinate to the toe joint

How to make a medical brace.
The method of claim 16,

The plurality of scale axes of the first state coordinate system are + X1 axis, -X1 axis, + Y1 axis, -Y1 axis, and + Z1 axis having the reflux joint reference point as the origin,

The scale of the + Z1 axis corresponds to the distance from the corresponding origin to the knee joint reference point,

The scale of the + Y1 axis corresponds to the distance from the origin to the outer end of the hip joint,

The scale of the -Y1 axis corresponds to the distance from the origin to the inner end of the femoral fracture,

The scale of the + X1 axis corresponds to the distance from the origin to the point of the patient model surface that meets when projecting in the + X1 axis direction,

The scale of the -X1 axis corresponds to the distance from the corresponding origin to the point of the patient model surface that meets during projection in the -X1 axis direction.

How to make a medical brace.
The method of claim 16,

The plurality of scale axes of the second state coordinate system are + X2 axis, + Y2 axis, -Y2 axis, and + Z2 axis having the origin outside the heel vicinity,

The scale of the + Z2 axis corresponds to the distance from the origin to the subtalar joint reference point,

The scale of the + Y2 axis corresponds to the distance from the origin to the outer end of the toe joint,

The scale of the -Y2 axis corresponds to the distance from the origin to the inner end of the toe joint,

The scale of the + X2 axis corresponds to the distance from the origin to the toe joint reference point

How to make a medical brace.
The method of claim 16,

The plurality of scale axes of the third state coordinate system are + X3 axis, + Y3 axis, -Y3 axis, + Z3 axis, and -Z3 axis having the toe joint reference point as the origin,

The scale of the + X3 axis corresponds to the distance from the origin to the toe end point,

The scale of the + Y3 axis corresponds to the distance from the origin to the outer end of the toe joint,

The scale of the -Y3 axis corresponds to the distance from the origin to the inner end of the toe joint,

The scale of the + Z3 axis corresponds to the distance from the corresponding origin to the point of the patient model surface that meets when projecting in the + Z3 axis direction,

The scale of the -Z3 axis corresponds to the distance from the corresponding origin to the point of the patient model surface that meets during projection in the -Z3 axis direction.

How to make a medical brace.
The method of claim 11,

Generating a 3D image by scanning the body part using a 3D scanner;

In the 3D printer, receiving the 3D brace model information and manufacturing the brace

Medical aids manufacturing method comprising a.
A computer-readable recording medium having recorded thereon a program for performing the method of claim 11.